US20100092655A1 - Clamp Mandrel Fixture And A Method Of Using The Same To Minimize Coating Defects - Google Patents
Clamp Mandrel Fixture And A Method Of Using The Same To Minimize Coating Defects Download PDFInfo
- Publication number
- US20100092655A1 US20100092655A1 US12/636,301 US63630109A US2010092655A1 US 20100092655 A1 US20100092655 A1 US 20100092655A1 US 63630109 A US63630109 A US 63630109A US 2010092655 A1 US2010092655 A1 US 2010092655A1
- Authority
- US
- United States
- Prior art keywords
- stent
- mandrel
- arm
- elements
- coating
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Images
Classifications
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05C—APPARATUS FOR APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05C13/00—Means for manipulating or holding work, e.g. for separate articles
- B05C13/02—Means for manipulating or holding work, e.g. for separate articles for particular articles
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05B—SPRAYING APPARATUS; ATOMISING APPARATUS; NOZZLES
- B05B13/00—Machines or plants for applying liquids or other fluent materials to surfaces of objects or other work by spraying, not covered by groups B05B1/00 - B05B11/00
- B05B13/02—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work
- B05B13/0221—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work characterised by the means for moving or conveying the objects or other work, e.g. conveyor belts
- B05B13/0228—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work characterised by the means for moving or conveying the objects or other work, e.g. conveyor belts the movement of the objects being rotative
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05B—SPRAYING APPARATUS; ATOMISING APPARATUS; NOZZLES
- B05B13/00—Machines or plants for applying liquids or other fluent materials to surfaces of objects or other work by spraying, not covered by groups B05B1/00 - B05B11/00
- B05B13/02—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work
- B05B13/04—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work the spray heads being moved during spraying operation
- B05B13/0442—Installation or apparatus for applying liquid or other fluent material to separate articles rotated during spraying operation
Definitions
- This invention relates to a clamp mandrel fixture for supporting a stent during the application of a coating composition.
- Blood vessel occlusions are commonly treated by mechanically enhancing blood flow in the affected vessels, such as by employing a stent.
- Stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of the passageway.
- stents are capable of being compressed, so that they can be inserted through small lumens via catheters, and then expanded to a larger diameter once they are at the desired location. Examples in the patent literature disclosing stents include U.S. Pat. No. 4,733,665 issued to Palmaz, U.S. Pat. No. 4,800,882 issued to Gianturco, and U.S. Pat. No. 4,886,062 issued to Wiktor.
- FIG. 1 illustrates a conventional stent 10 formed from a plurality of struts 12 .
- the plurality of struts 12 are radially expandable and interconnected by connecting elements 14 that are disposed between adjacent struts 12 , leaving lateral gaps or openings 16 between adjacent struts 12 .
- Struts 12 and connecting elements 14 define a tubular stent body having an outer, tissue-contacting surface and an inner surface.
- Stents are used not only for mechanical intervention but also as vehicles for providing biological therapy. Biological therapy can be achieved by medicating the stents. Medicated stents provide for the local administration of a therapeutic substance at the diseased site. Local delivery of a therapeutic substance is a preferred method of treatment because the substance is concentrated at a specific site and thus smaller total levels of medication can be administered in comparison to systemic dosages that often produce adverse or even toxic side effects for the patient.
- One method of medicating a stent involves the use of a polymeric carrier coated onto the surface of the stent.
- a composition including a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the blend is applied to the stent by immersing the stent in the composition or by spraying the composition onto the stent.
- the solvent is allowed to evaporate, leaving on the stent strut surfaces a coating of the polymer and the therapeutic substance impregnated in the polymer.
- a shortcoming of the above-described method of medicating a stent is the potential for coating defects. While some coating defects can be minimized by adjusting the coating parameters, other defects occur due to the nature of the interface between the stent and the apparatus on which the stent is supported during the coating process.
- a high degree of surface contact between the stent and the supporting apparatus can provide regions in which the liquid composition can flow, wick, and collect as the composition is applied. As the solvent evaporates, the excess composition hardens to form excess coating at and around the contact points between the stent and the supporting apparatus.
- the excess coating may stick to the apparatus, thereby removing some of the needed coating from the stent and leaving bare areas. Alternatively, the excess coating may stick to the stent, thereby leaving excess coating as clumps or pools on the struts or webbing between the struts.
- the present invention provides for a device for supporting a stent during the coating application process.
- the invention also provides for a method of coating the stent supported by the device.
- the device comprises a base, a mandrel extending from the base for penetrating at least partially through the longitudinal bore of the stent, and clamp elements extending from the base, the clamp elements configured to have an open configuration for allowing the mandrel to be inserted into the longitudinal bore of the stent, and a closed configuration for securing the stent on the mandrel during the application of the coating substance to the stent.
- the outer diameter of the mandrel can be smaller than the inner diameter of the stent.
- the base can include an indented portion, wherein each of the clamp elements can include a first segment extending over the indented portion of the base and a second segment extending out from the base such that an application of a force to the first segments of the clamp elements over the indented portion of the base causes the second segments to move away from each other towards the open configuration and the release of the force results in the second segments of the clamp elements to retract back towards each other. In the closed configuration, the clamp elements can compress against the mandrel.
- each of the clamp elements includes a first segment having a first length and a second segment having a second length, shorter than the first length, the second segments being bent in an inwardly direction towards the mandrel for engagement with the mandrel when the clamp elements are in the closed configuration.
- the first segments does not contact the stent when the clamp elements are in the closed configuration.
- the stent should not be capable of contacting the base when the stent is secured by the clamp elements on the mandrel.
- the device comprises a mandrel capable of extending at least partially through the hollow body of a stent, and an arm element for extending through a gaped region between the struts of the stent for holding the stent on the mandrel during the application of a coating composition to the stent.
- the device additionally includes a base member, wherein the mandrel extends from a center region of an end of the base member and the arm element extends from an edge of the end of the base member.
- the arm element can be characterized by a generally “L” shaped configuration having a long segment and a short segment.
- the long segment of the arm element can be generally parallel to the mandrel and the short segment of the arm element can be generally perpendicular to the mandrel, the short segment of the arm being configured to extend through the gaped region of the stent to compress against the mandrel.
- the diameter of the mandrel plus the length of the short segment of the arm element is greater than the outer diameter of the stent so as to prevent the stent from making contact with the long segment of the arm element during the application of the coating composition.
- the long segment of the arm element is capable of flexibly bending for engaging and disengaging the short segment of the arm element from the mandrel.
- the long segment of the arm element in a natural position, is in a generally linear configuration allowing the short segment of the arm element to be compressed against the mandrel.
- the length of the mandrel as measured from the end of the base member is longer than the length of the long segment of the arm element as measured from the end of the base member.
- a system for supporting a stent during the application of a coating substance to the stent comprises a base member and a first clamp member and a second clamp member extending from the base member, wherein a segment of each clamp member is configured to penetrate into a gaped region of a scaffolding network of the stent for supporting the stent on the base member during the application of the coating substance.
- a motor assembly is connected to the base member for rotating the stent about the longitudinal axis of the stent during the application of the coating substance.
- a mandrel extends from the base member for being inserted through the hollow tubular body of the stent, wherein the segments of the clamp members that are configured to penetrate into the gaped regions of the scaffolding network are configured to engage with the mandrel for securing the stent on the mandrel.
- the system can also include a nozzle assembly for spraying the coating substance onto the stent.
- a device for supporting a stent during the application of a coating substance to the stent comprises base member having a indented portion and a clamp member having a first segment disposed on the base member and extending over the indented portion of the base member, and a second segment extending out from one end of the base member for engagement with the stent.
- the application of pressure on a region of the first segment extending over the indented portion of the base member causes the clamp member to extend in an outwardly direction.
- the device can additionally include a second clamp member having a first segment disposed on the base member and extending over the indented portion of the base member, and a second segment extending out from the one end of the base member for engagement with the stent, wherein the application of a pressure on the first segments of the first and second clamp members causes the second segments of the first and second clamp members to bias away from one another and the release of the pressure from the first segments causes the first and second clamp members to bias towards each other for engagement of the stent.
- a method of coating a stent comprising positioning the stent on any of the embodiment of the support device and applying a coating composition to the stent.
- FIG. 1 illustrates a conventional stent.
- FIG. 2A illustrates a mounting assembly for supporting a stent in accordance with one embodiment of the invention.
- FIG. 2B illustrates an expanded perspective view of the mounting assembly in accordance with one embodiment of the present invention.
- FIG. 3A illustrates the clamp elements or arms of the mounting assembly in an open position in accordance with one embodiment of the present invention.
- FIG. 3B illustrates the clamp elements or arms of the mounting assembly in a closed position in accordance with one embodiment of the present invention.
- FIG. 4 is a magnified view of the interface between the mounting assembly and the stent in accordance with one embodiment of the present invention.
- FIGS. 5A-5C are end views illustrating the interface between the mounting assembly and the stent upon rotation during the coating process in accordance with one embodiment of the present invention.
- a mounting assembly 18 for supporting stent 10 is illustrated to include a base 20 , a center pin or mandrel 22 , and clamp or arm elements 24 .
- Base 20 can connect to a motor 26 , which provides rotational motion to mounting assembly 18 , as depicted by arrow 28 , during the coating process.
- Another motor 30 can also be provided for moving mounting assembly 18 and thus stent 10 in a linear direction, back and forth, along a rail 32 .
- Mandrel 22 extends longitudinally from base 20 , for example from a central region of the end of base 20 .
- mandrel 22 and base 20 can be manufactured as a single component.
- mandrel 22 and base 20 can be manufactured separately and later coupled to one another.
- base 20 can include a bore 34 for receiving mandrel 22 , as illustrated in FIG. 2B .
- Mandrel 22 can be press fitted into bore 34 or otherwise coupled to base 20 via, for example, welding or adhesives.
- mounting assembly 18 additionally includes a mandrel holder 36 for receiving mandrel 22 .
- mandrel holder 36 can be permanently or temporarily affixed within bore 34 such that surfaces 38 and 40 are flush upon assembly, and mandrel 22 can be, for example, press fit into mandrel holder 36 .
- a mandrel 22 manufactured separately from base 20 can also be disposable.
- Mandrel 22 can be of any suitable diameter d m and any suitable length l m that will allow for sufficient support of stent 10 during the coating process.
- Diameter d m should be small enough to allow maximum room for motion of stent 10 , thereby minimizing the possibility that the inner surface of stent 10 will stick to the outer surface of mandrel 22 during the coating process.
- Diameter d m should be large enough to provide sufficient support to stent 10 during rotation as well as against any downward forces exerted during the spraying and drying cycles of the coating process.
- Length l m should be longer than the length of stent 10 such that mandrel 22 extends beyond the mounted stent 10 at each of its opposing ends.
- mandrel 22 can have diameter d m that is about 20% of the inner diameter of stent 10 and length l m that is about 1 ⁇ 8 inch longer than the length of stent 10 .
- Mandrel 22 can be of any material that is capable of supporting stent 10 and that is compatible with the particular coating composition to be applied to stent 10 .
- mandrel 22 can be made of stainless steel, graphite or a composite.
- mandrel 22 can be made of nitinol, the super-elastic properties of which allow mandrels 22 of very small diameters d m to maintain suitable strength and flexibility throughout the coating process.
- Mounting assembly 18 is illustrated as having two arms or clamp elements 24 spaced 180° apart and extending from the and edge of the end of the base 20 .
- any number of arms 24 in any configuration can be used to adequately support stent 10 , and the embodiments of the present invention should not be limited to a mounting assembly 18 having two arms 24 spaced 180° apart as illustrated in the Figures. It should be noted, however, that the more arms 24 employed to support stent 10 , the more contact points that exist between mounting assembly 18 and stent 10 .
- each arm 24 is depicted in the Figures as a separate component, multiple arms 24 can be formed from a single component. For example, a wire can be bent into a U-shape such that one half of the wire functions as a first arm 24 and the other half of the wire functions as a second arm 24 .
- Each arm 24 includes an extension portion 42 extending into a support portion 44 at an angle ⁇ 1 via an elbow 46 .
- Angle ⁇ 1 can be at 90 degrees, for example.
- Extension portion 42 can couple arm 24 to base 20 .
- Arm 24 can be permanently or temporarily affixed to base 20 .
- Support portion 44 extends through opening 16 between struts 12 of mounted stent 10 to facilitate transient contact between mounting assembly 18 and stent 10 during the coating process.
- Extension and support portions 42 and 44 of arms 24 can be of any suitable dimensions.
- Extension portion 42 should have a length l e suitable to allow positioning of support portion 44 within a preselected opening 16 between struts 12 along mounted stent 10 .
- extension portions 42 are illustrated as having the same length l e , extension portions 42 on the same mounting assembly 18 can have different lengths l e such that their respective support portions 44 are staggered along the length of mounted stent 10 .
- Length l s of support portions 44 should be such that support tips 48 touch or compress against mandrel 22 when stent 10 is mounted thereon.
- a diameter d e of extension portion 42 and a diameter d s of support portion 44 should be capable of providing sufficient support to stent 10 during rotation as well as against any downward forces exerted during the spraying and drying cycles of the coating process while allowing sufficient movement of stent 10 to prevent permanent contact points between arms 24 and stent 10 .
- diameter d e of extension portion 42 tapers into a smaller diameter d s of support portion 44 , thereby optimizing both support and movement of mounted stent 10 .
- arms 24 can be of any material that is capable of supporting stent 10 and that is compatible with the particular coating composition to be applied to stent 10 .
- the material of which arms 24 are formed should also be sufficiently flexible to allow bending into a suitable shape as well as to facilitate easy loading and unloading of stent 10 .
- Arms 24 must be capable of opening and closing about mandrel 22 to facilitate loading and unloading of stent 10 .
- Arms 24 can be opened and closed in any suitable manner.
- arms 24 can be manually pulled open and pushed closed by an operator.
- arms 24 can be opened by, for example, sliding a ring along arm 24 toward base 20 and can be closed by sliding the ring along arm 24 toward support portion 44 .
- FIGS. 3A and 3B illustrate an embodiment in which arms 24 function together as a clamp to facilitate opening and closing.
- base 20 includes an indented portion 50 over which arms 24 extend. Pinching in extension portions 42 over indented portion 50 can open arms 24 . Lip 52 further allows extension portions 42 to flexibly spread apart. When pressure is released, extension portions 42 collapse back into a pinched configuration. In this embodiment, the natural position of extension portions 42 should be generally linear and parallel to that of mandrel 22 to allow the biasing of support portion 44 on mandrel 22 .
- the hourglass design of base 20 depicted in the Figures allows an operator to control the opening and closing of clamp-like arms 24 with one hand.
- mandrel 22 can be supported at its free end during the coating process in any suitable manner. Such support may help mounted stent 10 rotate more concentrically and may also help prevent a slight bend at the free end of mandrel 22 that may otherwise occur due to any downward forces exerted during the spraying and drying cycles of the coating process.
- the free end of mandrel 22 can be stabilized by allowing the free end to rest in a holder such as, for example, a V-block.
- a second rotatable base can be coupled to the free end of mandrel 22 .
- the second base can be coupled to a second set of arms.
- at least one base 20 should be disengagable from mandrel 22 so as to allow loading and unloading of stent 10 .
- clamp-like arms 24 of mounting assembly 18 can be opened by pinching extension portions 42 of arms 24 at depression 50 in the hourglass-shaped base 20 to cause support portions 44 of arms 24 to spread apart.
- Stent 10 can then be loaded onto mandrel 22 by, for example, holding mounting assembly 18 at an angle (e.g., 15° from horizontal) and sliding stent 10 over mandrel 22 toward base 20 .
- Clamp-like arms 24 can be closed about stent 10 by releasing the pressure applied to extension portions 42 , as depicted in FIG. 3B .
- FIG. 4 depicts the interface between a properly mounted stent 10 and mounting assembly 18 .
- Support portions 44 of arms 24 should protrude through openings 16 between struts 12 of stent 10 , and support tips 48 of support portions 44 should touch or compress against mandrel 22 .
- mounted stent 10 should not touch base 20 .
- a gap 54 between base 20 and stent 10 should be maintained to minimize the number of contact points between mounting assembly 18 and stent 10 as well as to maximize the movement of stent 10 during rotation.
- gap 54 can be about 1 mm to about 5 mm for stent 10 that is 13 mm to 38 mm long and about 1 mm to about 9 mm for stent 10 that is about 8 mm long.
- diameter d m of mandrel plus length l s of support portion 44 should be greater than the outer diameter of stent 10 to prevent stent 10 from contacting extension portions 42 .
- FIGS. 5A-5C illustrate the moving interface between a properly mounted stent 10 and mounting assembly 18 having two arms 24 a and 24 b spaced 180° apart upon rotation of mounting assembly 18 .
- support portions 44 a and 44 b of arms 24 a and 24 b respectively, protrude through openings 16 between struts 12 of stent 10 , and support tips 48 a and 48 b flush against mandrel 22 .
- mandrel 22 is rotated in the direction of arrow 28 , which can be either clock-wise or counter clock-wise, mounted stent 10 also rotates in the direction of arrow 28 .
- Such constant back and forth movement of stent 10 along support portions 44 upon rotation of mandrel 22 during the coating process allows the contact points between stent 10 and mounting assembly 18 to be transient rather than permanent, thereby preventing the coating material from flowing, wicking, collecting, and solidifying at or between arms 24 and stent 10 .
- the back and forth motion of stent 10 along arms 24 is enhanced by downward forces exerted throughout the coating process by atomization airflow during the spraying cycle and/or dryer airflow during the drying cycle.
- a spray apparatus such as EFD 780S spray device with VALVEMATE 7040 control system (manufactured by EFD Inc., East Buffalo, R.I.), can be used to apply a composition to a stent.
- EFD 780S spray device is an air-assisted external mixing atomizer.
- the composition is atomized into small droplets by air and uniformly applied to the stent surfaces.
- the atomization pressure can be maintained at a range of about 5 psi to about 20 psi, for example 15 psi.
- the droplet size depends on such factors as viscosity of the solution, surface tension of the solvent, and atomization pressure.
- the solution barrel pressure can be between 1 to 3.5 psi, for example 2.5 psi.
- the temperature of the nozzle can adjusted to a temperature other than ambient temperature during the spray process by the use of a heating block or other similar devices.
- the temperature of the nozzle can be between 45° to about 88°, the temperature depending on a variety of factors including the type and amount of polymer, solvent and drug used.
- the nozzle can be positioned at any suitable distance away form the stent, for example, about 10 mm to about 19 mm.
- mandrel 22 can be rotated about its own central longitudinal axis. Rotation of mandrel 22 can be from about 10 rpm to about 300 rpm, more narrowly from about 40 rpm to about 240 rpm. By way of example, mandrel 22 can rotate at about 100 rpm. Mandrel 22 can also be moved in a linear direction along the same axis. Mandrel 22 can be moved at about 1 mm/second to about 6 mm/second, for example about 3 mm/second, or for at least two passes, for example (i.e., back and forth past the spray nozzle).
- the flow rate of the solution from the spray nozzle can be from about 0.01 mg/second to about 1.0 mg/second, more narrowly about 0.1 mg/second.
- Multiple repetitions for applying the composition can be performed, wherein each repetition can be, for example, about 1 second to about 10 seconds in duration.
- the amount of coating applied by each repetition can be about 0.1 micrograms/cm 2 (of stent surface) to about 40 micrograms/cm 2 , for example less than about 2 micrograms/cm 2 per 5-second spray.
- Each repetition can be followed by removal of a significant amount of the solvent(s).
- the solvent can evaporate essentially upon contact with the stent.
- removal of the solvent can be induced by baking the stent in an oven at a mild temperature (e.g., 60° C.) for a suitable duration of time (e.g., 2-4 hours) or by the application of warm air.
- the application of warm air between each repetition prevents coating defects and minimizes interaction between the active agent and the solvent.
- the temperature of the warm air can be from about 30° C. to about 85° C., more narrowly from about 40° C. to about 55° C.
- the flow rate of the warm air can be from about 20 cubic feet/minute (CFM) (0.57 cubic meters/minute (CMM)) to about 80 CFM (2.27 CMM), more narrowly about 30 CFM (0.85 CMM) to about 40 CFM (1.13 CMM).
- the blower pressure can be, for example between 10 to 35 psi, more narrowly 12 to 15 psi and can be positioned at a distance of about 10 to 20 mm away from the stent.
- the warm air can be applied for about 3 seconds to about 60 seconds, more narrowly for about 10 seconds to about 20 seconds.
- warm air applications can be performed at a temperature of about 50° C., at a flow rate of about 40 CFM, and for about 10 seconds. Any suitable number of repetitions of applying the composition followed by removing the solvent(s) can be performed to form a coating of a desired thickness or weight. Excessive application of the polymer in a single application can, however, cause coating defects.
- wiping refers to the physical removal of excess coating from the surface of the stent
- centrifugation refers to rapid rotation of the stent about an axis of rotation.
- the excess coating can also be vacuumed off of the surface of the stent.
- the stent can be at least partially pre-expanded prior to the application of the composition.
- the stent can be radially expanded about 20% to about 60%, more narrowly about 27% to about 55%—the measurement being taken from the stent's inner diameter at an expanded position as compared to the inner diameter at the unexpanded position.
- the expansion of the stent, for increasing the interspace between the stent struts during the application of the composition can further prevent “cob web” formation between the stent struts.
- the composition can include a solvent and a polymer dissolved in the solvent.
- the composition can also include active agents, radiopaque elements, or radioactive isotopes.
- Representative examples of polymers that can be used to coat a stent include ethylene vinyl alcohol copolymer (commonly known by the generic name EVOH or by the trade name EVAL), poly(hydroxyvalerate); poly(L-lactic acid); polycaprolactone; poly(lactide-co-glycolide); poly(hydroxybutyrate); poly(hydroxybutyrate-co-valerate); polydioxanone; polyorthoester; polyanhydride; poly(glycolic acid); poly(D,L-lactic acid); poly(glycolic acid-co-trimethylene carbonate); polyphosphoester; polyphosphoester urethane; poly(amino acids); cyanoacrylates; poly(trimethylene carbonate); poly(iminocarbonate); copoly(ether-esters) (e.g.,
- PEO/PLA polyalkylene oxalates; polyphosphazenes; biomolecules, such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid; polyurethanes; silicones; polyesters; polyolefins; polyisobutylene and ethylene-alphaolefin copolymers; acrylic polymers and copolymers; vinyl halide polymers and copolymers, such as polyvinyl chloride; polyvinyl ethers, such as polyvinyl methyl ether; polyvinylidene halides, such as polyvinylidene fluoride and polyvinylidene chloride; polyacrylonitrile; polyvinyl ketones; polyvinyl aromatics, such as polystyrene; polyvinyl esters, such as polyvinyl acetate; copolymers of vinyl monomers with each other and olefins, such as ethylene-methyl methacrylate copolymers, acryl
- solvent is defined as a liquid substance or composition that is compatible with the polymer and is capable of dissolving the polymer at the concentration desired in the composition.
- solvents include, but are not limited to, dimethylsulfoxide (DMSO), chloroform, acetone, water (buffered saline), xylene, methanol, ethanol, 1-propanol, tetrahydrofuran, 1-butanone, dimethylformamide, dimethylacetamide, cyclohexanone, ethyl acetate, methylethylketone, propylene glycol monomethylether, isopropanol, isopropanol admixed with water, N-methyl pyrrolidinone, toluene, and combinations thereof.
- the active agent can be for inhibiting the activity of vascular smooth muscle cells. More specifically, the active agent can be aimed at inhibiting abnormal or inappropriate migration and/or proliferation of smooth muscle cells for the inhibition of restenosis.
- the active agent can also include any substance capable of exerting a therapeutic or prophylactic effect in the practice of the present invention.
- the agent can be for enhancing wound healing in a vascular site or improving the structural and elastic properties of the vascular site.
- agents include antiproliferative substances such as actinomycin D, or derivatives and analogs thereof (manufactured by Sigma-Aldrich 1001 West Saint Paul Avenue, Milwaukee, Wis. 53233; or COSMEGEN available from Merck).
- actinomycin D examples include dactinomycin, actinomycin IV, actinomycin I 1 , actinomycin X 1 , and actinomycin C 1 .
- the active agent can also fall under the genus of antineoplastic, antiinflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances.
- antineoplastics and/or antimitotics include paclitaxel (e.g. TAXOL® by Bristol-Myers Squibb Co., Stamford, Conn.), docetaxel (e.g.
- Taxotere® from Aventis S.A., Frankfurt, Germany methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g. Adriamycin® from Pharmacia & Upjohn, Peapack N.J.), and mitomycin (e.g. Mutamycin® from Bristol-Myers Squibb Co., Stamford, Conn.).
- antiplatelets examples include sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogues, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin), dipyridamole, glycoprotein IIb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, and thrombin inhibitors such as AngiomaxTM (Biogen, Inc., Cambridge, Mass.).
- AngiomaxTM Biogen, Inc., Cambridge, Mass.
- cytostatic or antiproliferative agents examples include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g. Capoten® and Capozide® from Bristol-Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g.
- calcium channel blockers such as nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck & Co., Inc., Whitehouse Station, N.J.), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids, thioprotease inhibitors, triazolopyrimidine (a PDGF antagonist), and nitric oxide.
- PDGF Platelet-Derived Growth Factor
- an antiallergic agent is permirolast potassium.
- Other therapeutic substances or agents that may be appropriate include alpha-interferon, genetically engineered epithelial cells, rapamycin and dexamethasone. Exposure of the active ingredient to the composition should not adversely alter the active ingredient's composition or characteristic. Accordingly, the particular active ingredient is selected for compatibility with the solvent or blended polymer-solvent.
Landscapes
- Media Introduction/Drainage Providing Device (AREA)
Abstract
Description
- This application is continuation of application Ser. No. 11/437,589 filed May 19, 2006, which is a divisional of application Ser. No. 10/319,042 filed Dec. 12, 2002, now U.S. Pat. No. 7,074,276, the contents of both applications are incorporated herein by reference.
- 1. Field of the Invention
- This invention relates to a clamp mandrel fixture for supporting a stent during the application of a coating composition.
- 2. Description of the Background
- Blood vessel occlusions are commonly treated by mechanically enhancing blood flow in the affected vessels, such as by employing a stent. Stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of the passageway. Typically stents are capable of being compressed, so that they can be inserted through small lumens via catheters, and then expanded to a larger diameter once they are at the desired location. Examples in the patent literature disclosing stents include U.S. Pat. No. 4,733,665 issued to Palmaz, U.S. Pat. No. 4,800,882 issued to Gianturco, and U.S. Pat. No. 4,886,062 issued to Wiktor.
-
FIG. 1 illustrates aconventional stent 10 formed from a plurality ofstruts 12. The plurality ofstruts 12 are radially expandable and interconnected by connectingelements 14 that are disposed betweenadjacent struts 12, leaving lateral gaps oropenings 16 betweenadjacent struts 12.Struts 12 and connectingelements 14 define a tubular stent body having an outer, tissue-contacting surface and an inner surface. - Stents are used not only for mechanical intervention but also as vehicles for providing biological therapy. Biological therapy can be achieved by medicating the stents. Medicated stents provide for the local administration of a therapeutic substance at the diseased site. Local delivery of a therapeutic substance is a preferred method of treatment because the substance is concentrated at a specific site and thus smaller total levels of medication can be administered in comparison to systemic dosages that often produce adverse or even toxic side effects for the patient.
- One method of medicating a stent involves the use of a polymeric carrier coated onto the surface of the stent. A composition including a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the blend is applied to the stent by immersing the stent in the composition or by spraying the composition onto the stent. The solvent is allowed to evaporate, leaving on the stent strut surfaces a coating of the polymer and the therapeutic substance impregnated in the polymer.
- A shortcoming of the above-described method of medicating a stent is the potential for coating defects. While some coating defects can be minimized by adjusting the coating parameters, other defects occur due to the nature of the interface between the stent and the apparatus on which the stent is supported during the coating process. A high degree of surface contact between the stent and the supporting apparatus can provide regions in which the liquid composition can flow, wick, and collect as the composition is applied. As the solvent evaporates, the excess composition hardens to form excess coating at and around the contact points between the stent and the supporting apparatus. Upon the removal of the coated stent from the supporting apparatus, the excess coating may stick to the apparatus, thereby removing some of the needed coating from the stent and leaving bare areas. Alternatively, the excess coating may stick to the stent, thereby leaving excess coating as clumps or pools on the struts or webbing between the struts.
- Thus, it is desirable to minimize the interface between the stent and the apparatus supporting the stent during the coating process to minimize coating defects. Accordingly, the present invention provides for a device for supporting a stent during the coating application process. The invention also provides for a method of coating the stent supported by the device.
- A device for supporting a stent during the application of a coating substance to the stent is provided. In one embodiment, the device comprises a base, a mandrel extending from the base for penetrating at least partially through the longitudinal bore of the stent, and clamp elements extending from the base, the clamp elements configured to have an open configuration for allowing the mandrel to be inserted into the longitudinal bore of the stent, and a closed configuration for securing the stent on the mandrel during the application of the coating substance to the stent.
- The outer diameter of the mandrel can be smaller than the inner diameter of the stent. In one variation, the base can include an indented portion, wherein each of the clamp elements can include a first segment extending over the indented portion of the base and a second segment extending out from the base such that an application of a force to the first segments of the clamp elements over the indented portion of the base causes the second segments to move away from each other towards the open configuration and the release of the force results in the second segments of the clamp elements to retract back towards each other. In the closed configuration, the clamp elements can compress against the mandrel. In one embodiment, each of the clamp elements includes a first segment having a first length and a second segment having a second length, shorter than the first length, the second segments being bent in an inwardly direction towards the mandrel for engagement with the mandrel when the clamp elements are in the closed configuration. The first segments does not contact the stent when the clamp elements are in the closed configuration. Moreover, the stent should not be capable of contacting the base when the stent is secured by the clamp elements on the mandrel.
- In accordance with another embodiment, the device comprises a mandrel capable of extending at least partially through the hollow body of a stent, and an arm element for extending through a gaped region between the struts of the stent for holding the stent on the mandrel during the application of a coating composition to the stent. In one embodiment, the device additionally includes a base member, wherein the mandrel extends from a center region of an end of the base member and the arm element extends from an edge of the end of the base member. The arm element can be characterized by a generally “L” shaped configuration having a long segment and a short segment. The long segment of the arm element can be generally parallel to the mandrel and the short segment of the arm element can be generally perpendicular to the mandrel, the short segment of the arm being configured to extend through the gaped region of the stent to compress against the mandrel. In one variation, the diameter of the mandrel plus the length of the short segment of the arm element is greater than the outer diameter of the stent so as to prevent the stent from making contact with the long segment of the arm element during the application of the coating composition. The long segment of the arm element is capable of flexibly bending for engaging and disengaging the short segment of the arm element from the mandrel. In one embodiment, in a natural position, the long segment of the arm element is in a generally linear configuration allowing the short segment of the arm element to be compressed against the mandrel. In another embodiment, the length of the mandrel as measured from the end of the base member is longer than the length of the long segment of the arm element as measured from the end of the base member.
- In accordance with yet another embodiment of the invention, a system for supporting a stent during the application of a coating substance to the stent is provided. The system comprises a base member and a first clamp member and a second clamp member extending from the base member, wherein a segment of each clamp member is configured to penetrate into a gaped region of a scaffolding network of the stent for supporting the stent on the base member during the application of the coating substance. In one embodiment, a motor assembly is connected to the base member for rotating the stent about the longitudinal axis of the stent during the application of the coating substance. In another embodiment, a mandrel extends from the base member for being inserted through the hollow tubular body of the stent, wherein the segments of the clamp members that are configured to penetrate into the gaped regions of the scaffolding network are configured to engage with the mandrel for securing the stent on the mandrel. The system can also include a nozzle assembly for spraying the coating substance onto the stent.
- In accordance with yet another embodiment, a device for supporting a stent during the application of a coating substance to the stent is provided, the device comprises base member having a indented portion and a clamp member having a first segment disposed on the base member and extending over the indented portion of the base member, and a second segment extending out from one end of the base member for engagement with the stent. The application of pressure on a region of the first segment extending over the indented portion of the base member causes the clamp member to extend in an outwardly direction. The device can additionally include a second clamp member having a first segment disposed on the base member and extending over the indented portion of the base member, and a second segment extending out from the one end of the base member for engagement with the stent, wherein the application of a pressure on the first segments of the first and second clamp members causes the second segments of the first and second clamp members to bias away from one another and the release of the pressure from the first segments causes the first and second clamp members to bias towards each other for engagement of the stent.
- A method of coating a stent is also provided comprising positioning the stent on any of the embodiment of the support device and applying a coating composition to the stent.
-
FIG. 1 illustrates a conventional stent. -
FIG. 2A illustrates a mounting assembly for supporting a stent in accordance with one embodiment of the invention. -
FIG. 2B illustrates an expanded perspective view of the mounting assembly in accordance with one embodiment of the present invention. -
FIG. 3A illustrates the clamp elements or arms of the mounting assembly in an open position in accordance with one embodiment of the present invention. -
FIG. 3B illustrates the clamp elements or arms of the mounting assembly in a closed position in accordance with one embodiment of the present invention. -
FIG. 4 is a magnified view of the interface between the mounting assembly and the stent in accordance with one embodiment of the present invention. -
FIGS. 5A-5C are end views illustrating the interface between the mounting assembly and the stent upon rotation during the coating process in accordance with one embodiment of the present invention. - Referring to
FIG. 2A , a mountingassembly 18 for supportingstent 10 is illustrated to include abase 20, a center pin ormandrel 22, and clamp orarm elements 24.Base 20 can connect to amotor 26, which provides rotational motion to mountingassembly 18, as depicted byarrow 28, during the coating process. Anothermotor 30 can also be provided for moving mountingassembly 18 and thusstent 10 in a linear direction, back and forth, along arail 32. -
Mandrel 22 extends longitudinally frombase 20, for example from a central region of the end ofbase 20. In accordance with one embodiment,mandrel 22 andbase 20 can be manufactured as a single component. Alternatively,mandrel 22 andbase 20 can be manufactured separately and later coupled to one another. In such an embodiment,base 20 can include abore 34 for receivingmandrel 22, as illustrated inFIG. 2B .Mandrel 22 can be press fitted intobore 34 or otherwise coupled tobase 20 via, for example, welding or adhesives. In the depicted embodiment, mountingassembly 18 additionally includes amandrel holder 36 for receivingmandrel 22. In such an embodiment,mandrel holder 36 can be permanently or temporarily affixed withinbore 34 such that surfaces 38 and 40 are flush upon assembly, andmandrel 22 can be, for example, press fit intomandrel holder 36. Amandrel 22 manufactured separately frombase 20 can also be disposable. -
Mandrel 22 can be of any suitable diameter dm and any suitable length lm that will allow for sufficient support ofstent 10 during the coating process. Diameter dm should be small enough to allow maximum room for motion ofstent 10, thereby minimizing the possibility that the inner surface ofstent 10 will stick to the outer surface ofmandrel 22 during the coating process. Diameter dm should be large enough to provide sufficient support tostent 10 during rotation as well as against any downward forces exerted during the spraying and drying cycles of the coating process. Length lm should be longer than the length ofstent 10 such thatmandrel 22 extends beyond the mountedstent 10 at each of its opposing ends. By way of example and not limitation,mandrel 22 can have diameter dm that is about 20% of the inner diameter ofstent 10 and length lm that is about ⅛ inch longer than the length ofstent 10. -
Mandrel 22 can be of any material that is capable of supportingstent 10 and that is compatible with the particular coating composition to be applied tostent 10. For example,mandrel 22 can be made of stainless steel, graphite or a composite. In another embodiment,mandrel 22 can be made of nitinol, the super-elastic properties of which allowmandrels 22 of very small diameters dm to maintain suitable strength and flexibility throughout the coating process. - Mounting
assembly 18 is illustrated as having two arms or clampelements 24 spaced 180° apart and extending from the and edge of the end of thebase 20. In commercially useful embodiments, any number ofarms 24 in any configuration can be used to adequately supportstent 10, and the embodiments of the present invention should not be limited to a mountingassembly 18 having twoarms 24 spaced 180° apart as illustrated in the Figures. It should be noted, however, that themore arms 24 employed to supportstent 10, the more contact points that exist between mountingassembly 18 andstent 10. In addition, although eacharm 24 is depicted in the Figures as a separate component,multiple arms 24 can be formed from a single component. For example, a wire can be bent into a U-shape such that one half of the wire functions as afirst arm 24 and the other half of the wire functions as asecond arm 24. - Each
arm 24 includes anextension portion 42 extending into asupport portion 44 at an angle φ1 via anelbow 46. Angle φ1 can be at 90 degrees, for example.Extension portion 42 can couplearm 24 tobase 20.Arm 24 can be permanently or temporarily affixed tobase 20.Support portion 44 extends through opening 16 betweenstruts 12 of mountedstent 10 to facilitate transient contact between mountingassembly 18 andstent 10 during the coating process. - Extension and
support portions arms 24 can be of any suitable dimensions.Extension portion 42 should have a length le suitable to allow positioning ofsupport portion 44 within apreselected opening 16 betweenstruts 12 along mountedstent 10. Althoughextension portions 42 are illustrated as having the same length le,extension portions 42 on the same mountingassembly 18 can have different lengths le such that theirrespective support portions 44 are staggered along the length of mountedstent 10. Length ls ofsupport portions 44 should be such thatsupport tips 48 touch or compress againstmandrel 22 whenstent 10 is mounted thereon.Support portions 44 that are too short may cause mountedstent 10 to slip off mountingassembly 18 during the coating process, whilesupport portions 44 that are too long run may hinder movement ofstent 10 during the coating process. A diameter de ofextension portion 42 and a diameter ds ofsupport portion 44 should be capable of providing sufficient support tostent 10 during rotation as well as against any downward forces exerted during the spraying and drying cycles of the coating process while allowing sufficient movement ofstent 10 to prevent permanent contact points betweenarms 24 andstent 10. In one embodiment, diameter de ofextension portion 42 tapers into a smaller diameter ds ofsupport portion 44, thereby optimizing both support and movement of mountedstent 10. - As with
mandrel 22 discussed above,arms 24 can be of any material that is capable of supportingstent 10 and that is compatible with the particular coating composition to be applied tostent 10. The material of whicharms 24 are formed should also be sufficiently flexible to allow bending into a suitable shape as well as to facilitate easy loading and unloading ofstent 10. -
Arms 24 must be capable of opening and closing aboutmandrel 22 to facilitate loading and unloading ofstent 10.Arms 24 can be opened and closed in any suitable manner. For example, in one embodiment,arms 24 can be manually pulled open and pushed closed by an operator. In another embodiment,arms 24 can be opened by, for example, sliding a ring alongarm 24 towardbase 20 and can be closed by sliding the ring alongarm 24 towardsupport portion 44. -
FIGS. 3A and 3B illustrate an embodiment in whicharms 24 function together as a clamp to facilitate opening and closing. In such an embodiment,base 20 includes anindented portion 50 over whicharms 24 extend. Pinching inextension portions 42 overindented portion 50 can openarms 24.Lip 52 further allowsextension portions 42 to flexibly spread apart. When pressure is released,extension portions 42 collapse back into a pinched configuration. In this embodiment, the natural position ofextension portions 42 should be generally linear and parallel to that ofmandrel 22 to allow the biasing ofsupport portion 44 onmandrel 22. The hourglass design ofbase 20 depicted in the Figures allows an operator to control the opening and closing of clamp-like arms 24 with one hand. - Although mounting
assembly 18 is illustrated such thatarms 24 are attached tobase 20,arms 24 can also be attached tomandrel 22 such thatbase 20 is not required. In other commercially useful embodiments,mandrel 22 can be supported at its free end during the coating process in any suitable manner. Such support may help mountedstent 10 rotate more concentrically and may also help prevent a slight bend at the free end ofmandrel 22 that may otherwise occur due to any downward forces exerted during the spraying and drying cycles of the coating process. In one such embodiment, the free end ofmandrel 22 can be stabilized by allowing the free end to rest in a holder such as, for example, a V-block. In another embodiment, a second rotatable base can be coupled to the free end ofmandrel 22. The second base can be coupled to a second set of arms. In such an embodiment, at least onebase 20 should be disengagable frommandrel 22 so as to allow loading and unloading ofstent 10. - The following description is being provided by way of illustration and is not intended to limit the embodiments of mounting
assembly 18, the method of loadingstent 10 onto mountingassembly 18, or the method of using mountingassembly 18 tocoat stent 10. Referring again toFIG. 3A , clamp-like arms 24 of mountingassembly 18 can be opened by pinchingextension portions 42 ofarms 24 atdepression 50 in the hourglass-shapedbase 20 to causesupport portions 44 ofarms 24 to spread apart.Stent 10 can then be loaded ontomandrel 22 by, for example, holding mountingassembly 18 at an angle (e.g., 15° from horizontal) and slidingstent 10 overmandrel 22 towardbase 20. Clamp-like arms 24 can be closed aboutstent 10 by releasing the pressure applied toextension portions 42, as depicted inFIG. 3B . -
FIG. 4 depicts the interface between a properly mountedstent 10 and mountingassembly 18.Support portions 44 ofarms 24 should protrude throughopenings 16 betweenstruts 12 ofstent 10, and supporttips 48 ofsupport portions 44 should touch or compress againstmandrel 22. As illustrated, mountedstent 10 should not touchbase 20. Agap 54 betweenbase 20 andstent 10 should be maintained to minimize the number of contact points between mountingassembly 18 andstent 10 as well as to maximize the movement ofstent 10 during rotation. By way of example and not limitation,gap 54 can be about 1 mm to about 5 mm forstent 10 that is 13 mm to 38 mm long and about 1 mm to about 9 mm forstent 10 that is about 8 mm long. Additionally, as best illustrated by the Figures, diameter dm of mandrel plus length ls ofsupport portion 44 should be greater than the outer diameter ofstent 10 to preventstent 10 from contactingextension portions 42. -
FIGS. 5A-5C illustrate the moving interface between a properly mountedstent 10 and mountingassembly 18 having twoarms assembly 18. As depicted inFIG. 5A ,support portions arms openings 16 betweenstruts 12 ofstent 10, and supporttips mandrel 22. Asmandrel 22 is rotated in the direction ofarrow 28, which can be either clock-wise or counter clock-wise,mounted stent 10 also rotates in the direction ofarrow 28. Asarms stent 10 slides downward alongsupport portions arrow 56, as depicted inFIG. 5B , untilarms FIG. 5C upon rotation one half-turn or 180°. Continued rotation ofmandrel 22 allowsstent 10 to move back and forth alongsupport portions elbows double arrow 58 depicted inFIG. 5C . Such constant back and forth movement ofstent 10 alongsupport portions 44 upon rotation ofmandrel 22 during the coating process allows the contact points betweenstent 10 and mountingassembly 18 to be transient rather than permanent, thereby preventing the coating material from flowing, wicking, collecting, and solidifying at or betweenarms 24 andstent 10. In some embodiments, the back and forth motion ofstent 10 alongarms 24 is enhanced by downward forces exerted throughout the coating process by atomization airflow during the spraying cycle and/or dryer airflow during the drying cycle. - The following method of application is being provided by way of illustration and is not intended to limit the embodiments of the present invention. A spray apparatus, such as EFD 780S spray device with VALVEMATE 7040 control system (manufactured by EFD Inc., East Providence, R.I.), can be used to apply a composition to a stent. EFD 780S spray device is an air-assisted external mixing atomizer. The composition is atomized into small droplets by air and uniformly applied to the stent surfaces. The atomization pressure can be maintained at a range of about 5 psi to about 20 psi, for example 15 psi. The droplet size depends on such factors as viscosity of the solution, surface tension of the solvent, and atomization pressure. Other types of spray applicators, including air-assisted internal mixing atomizers and ultrasonic applicators, can also be used for the application of the composition. The solution barrel pressure can be between 1 to 3.5 psi, for example 2.5 psi. The temperature of the nozzle can adjusted to a temperature other than ambient temperature during the spray process by the use of a heating block or other similar devices. For example, the temperature of the nozzle can be between 45° to about 88°, the temperature depending on a variety of factors including the type and amount of polymer, solvent and drug used. The nozzle can be positioned at any suitable distance away form the stent, for example, about 10 mm to about 19 mm.
- During the application of the composition,
mandrel 22 can be rotated about its own central longitudinal axis. Rotation ofmandrel 22 can be from about 10 rpm to about 300 rpm, more narrowly from about 40 rpm to about 240 rpm. By way of example,mandrel 22 can rotate at about 100 rpm.Mandrel 22 can also be moved in a linear direction along the same axis.Mandrel 22 can be moved at about 1 mm/second to about 6 mm/second, for example about 3 mm/second, or for at least two passes, for example (i.e., back and forth past the spray nozzle). The flow rate of the solution from the spray nozzle can be from about 0.01 mg/second to about 1.0 mg/second, more narrowly about 0.1 mg/second. Multiple repetitions for applying the composition can be performed, wherein each repetition can be, for example, about 1 second to about 10 seconds in duration. The amount of coating applied by each repetition can be about 0.1 micrograms/cm2 (of stent surface) to about 40 micrograms/cm2, for example less than about 2 micrograms/cm2 per 5-second spray. - Each repetition can be followed by removal of a significant amount of the solvent(s). Depending on the volatility of the particular solvent employed, the solvent can evaporate essentially upon contact with the stent. Alternatively, removal of the solvent can be induced by baking the stent in an oven at a mild temperature (e.g., 60° C.) for a suitable duration of time (e.g., 2-4 hours) or by the application of warm air. The application of warm air between each repetition prevents coating defects and minimizes interaction between the active agent and the solvent. The temperature of the warm air can be from about 30° C. to about 85° C., more narrowly from about 40° C. to about 55° C. The flow rate of the warm air can be from about 20 cubic feet/minute (CFM) (0.57 cubic meters/minute (CMM)) to about 80 CFM (2.27 CMM), more narrowly about 30 CFM (0.85 CMM) to about 40 CFM (1.13 CMM). The blower pressure can be, for example between 10 to 35 psi, more narrowly 12 to 15 psi and can be positioned at a distance of about 10 to 20 mm away from the stent. The warm air can be applied for about 3 seconds to about 60 seconds, more narrowly for about 10 seconds to about 20 seconds. By way of example, warm air applications can be performed at a temperature of about 50° C., at a flow rate of about 40 CFM, and for about 10 seconds. Any suitable number of repetitions of applying the composition followed by removing the solvent(s) can be performed to form a coating of a desired thickness or weight. Excessive application of the polymer in a single application can, however, cause coating defects.
- Operations such as wiping, centrifugation, or other web clearing acts can also be performed to achieve a more uniform coating. Briefly, wiping refers to the physical removal of excess coating from the surface of the stent; and centrifugation refers to rapid rotation of the stent about an axis of rotation. The excess coating can also be vacuumed off of the surface of the stent.
- In accordance with one embodiment, the stent can be at least partially pre-expanded prior to the application of the composition. For example, the stent can be radially expanded about 20% to about 60%, more narrowly about 27% to about 55%—the measurement being taken from the stent's inner diameter at an expanded position as compared to the inner diameter at the unexpanded position. The expansion of the stent, for increasing the interspace between the stent struts during the application of the composition, can further prevent “cob web” formation between the stent struts.
- In accordance with one embodiment, the composition can include a solvent and a polymer dissolved in the solvent. The composition can also include active agents, radiopaque elements, or radioactive isotopes. Representative examples of polymers that can be used to coat a stent include ethylene vinyl alcohol copolymer (commonly known by the generic name EVOH or by the trade name EVAL), poly(hydroxyvalerate); poly(L-lactic acid); polycaprolactone; poly(lactide-co-glycolide); poly(hydroxybutyrate); poly(hydroxybutyrate-co-valerate); polydioxanone; polyorthoester; polyanhydride; poly(glycolic acid); poly(D,L-lactic acid); poly(glycolic acid-co-trimethylene carbonate); polyphosphoester; polyphosphoester urethane; poly(amino acids); cyanoacrylates; poly(trimethylene carbonate); poly(iminocarbonate); copoly(ether-esters) (e.g. PEO/PLA); polyalkylene oxalates; polyphosphazenes; biomolecules, such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid; polyurethanes; silicones; polyesters; polyolefins; polyisobutylene and ethylene-alphaolefin copolymers; acrylic polymers and copolymers; vinyl halide polymers and copolymers, such as polyvinyl chloride; polyvinyl ethers, such as polyvinyl methyl ether; polyvinylidene halides, such as polyvinylidene fluoride and polyvinylidene chloride; polyacrylonitrile; polyvinyl ketones; polyvinyl aromatics, such as polystyrene; polyvinyl esters, such as polyvinyl acetate; copolymers of vinyl monomers with each other and olefins, such as ethylene-methyl methacrylate copolymers, acrylonitrile-styrene copolymers, ABS resins, and ethylene-vinyl acetate copolymers; polyamides, such as Nylon 66 and polycaprolactam; alkyd resins; polycarbonates; polyoxymethylenes; polyimides; polyethers; epoxy resins; polyurethanes; rayon; rayon-triacetate; cellulose; cellulose acetate; cellulose butyrate; cellulose acetate butyrate; cellophane; cellulose nitrate; cellulose propionate; cellulose ethers; and carboxymethyl cellulose.
- “Solvent” is defined as a liquid substance or composition that is compatible with the polymer and is capable of dissolving the polymer at the concentration desired in the composition. Examples of solvents include, but are not limited to, dimethylsulfoxide (DMSO), chloroform, acetone, water (buffered saline), xylene, methanol, ethanol, 1-propanol, tetrahydrofuran, 1-butanone, dimethylformamide, dimethylacetamide, cyclohexanone, ethyl acetate, methylethylketone, propylene glycol monomethylether, isopropanol, isopropanol admixed with water, N-methyl pyrrolidinone, toluene, and combinations thereof.
- The active agent can be for inhibiting the activity of vascular smooth muscle cells. More specifically, the active agent can be aimed at inhibiting abnormal or inappropriate migration and/or proliferation of smooth muscle cells for the inhibition of restenosis. The active agent can also include any substance capable of exerting a therapeutic or prophylactic effect in the practice of the present invention. For example, the agent can be for enhancing wound healing in a vascular site or improving the structural and elastic properties of the vascular site. Examples of agents include antiproliferative substances such as actinomycin D, or derivatives and analogs thereof (manufactured by Sigma-Aldrich 1001 West Saint Paul Avenue, Milwaukee, Wis. 53233; or COSMEGEN available from Merck). Synonyms of actinomycin D include dactinomycin, actinomycin IV, actinomycin I1, actinomycin X1, and actinomycin C1. The active agent can also fall under the genus of antineoplastic, antiinflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances. Examples of such antineoplastics and/or antimitotics include paclitaxel (e.g. TAXOL® by Bristol-Myers Squibb Co., Stamford, Conn.), docetaxel (e.g. Taxotere®, from Aventis S.A., Frankfurt, Germany) methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g. Adriamycin® from Pharmacia & Upjohn, Peapack N.J.), and mitomycin (e.g. Mutamycin® from Bristol-Myers Squibb Co., Stamford, Conn.). Examples of such antiplatelets, anticoagulants, antifibrin, and antithrombins include sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogues, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin), dipyridamole, glycoprotein IIb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, and thrombin inhibitors such as Angiomax™ (Biogen, Inc., Cambridge, Mass.). Examples of such cytostatic or antiproliferative agents include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g. Capoten® and Capozide® from Bristol-Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g. Prinivil® and Prinzide® from Merck & Co., Inc., Whitehouse Station, N.J.); calcium channel blockers (such as nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck & Co., Inc., Whitehouse Station, N.J.), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids, thioprotease inhibitors, triazolopyrimidine (a PDGF antagonist), and nitric oxide. An example of an antiallergic agent is permirolast potassium. Other therapeutic substances or agents that may be appropriate include alpha-interferon, genetically engineered epithelial cells, rapamycin and dexamethasone. Exposure of the active ingredient to the composition should not adversely alter the active ingredient's composition or characteristic. Accordingly, the particular active ingredient is selected for compatibility with the solvent or blended polymer-solvent.
- While particular embodiments of the present invention have been shown and described, it will be obvious to those skilled in the art that changes and modifications can be made without departing from this invention in its broader aspects. Therefore, the appended claims are to encompass within their scope all such changes and modifications as fall within the true spirit and scope of this invention.
Claims (20)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/636,301 US7901728B2 (en) | 2002-12-12 | 2009-12-11 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/319,042 US7074276B1 (en) | 2002-12-12 | 2002-12-12 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US11/437,589 US7648725B2 (en) | 2002-12-12 | 2006-05-19 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US12/636,301 US7901728B2 (en) | 2002-12-12 | 2009-12-11 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/437,589 Continuation US7648725B2 (en) | 2002-12-12 | 2006-05-19 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
Publications (2)
Publication Number | Publication Date |
---|---|
US20100092655A1 true US20100092655A1 (en) | 2010-04-15 |
US7901728B2 US7901728B2 (en) | 2011-03-08 |
Family
ID=36644027
Family Applications (4)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/319,042 Expired - Lifetime US7074276B1 (en) | 2002-12-12 | 2002-12-12 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US11/437,589 Expired - Fee Related US7648725B2 (en) | 2002-12-12 | 2006-05-19 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US11/437,593 Expired - Fee Related US7572336B2 (en) | 2002-12-12 | 2006-05-19 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US12/636,301 Expired - Fee Related US7901728B2 (en) | 2002-12-12 | 2009-12-11 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
Family Applications Before (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/319,042 Expired - Lifetime US7074276B1 (en) | 2002-12-12 | 2002-12-12 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US11/437,589 Expired - Fee Related US7648725B2 (en) | 2002-12-12 | 2006-05-19 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US11/437,593 Expired - Fee Related US7572336B2 (en) | 2002-12-12 | 2006-05-19 | Clamp mandrel fixture and a method of using the same to minimize coating defects |
Country Status (1)
Country | Link |
---|---|
US (4) | US7074276B1 (en) |
Families Citing this family (39)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7323209B1 (en) * | 2003-05-15 | 2008-01-29 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating stents |
US20050208093A1 (en) | 2004-03-22 | 2005-09-22 | Thierry Glauser | Phosphoryl choline coating compositions |
US7735449B1 (en) * | 2005-07-28 | 2010-06-15 | Advanced Cardiovascular Systems, Inc. | Stent fixture having rounded support structures and method for use thereof |
US8003156B2 (en) | 2006-05-04 | 2011-08-23 | Advanced Cardiovascular Systems, Inc. | Rotatable support elements for stents |
US8685430B1 (en) | 2006-07-14 | 2014-04-01 | Abbott Cardiovascular Systems Inc. | Tailored aliphatic polyesters for stent coatings |
US8952123B1 (en) | 2006-08-02 | 2015-02-10 | Abbott Cardiovascular Systems Inc. | Dioxanone-based copolymers for implantable devices |
US20080175882A1 (en) * | 2007-01-23 | 2008-07-24 | Trollsas Mikael O | Polymers of aliphatic thioester |
US10155881B2 (en) * | 2007-05-30 | 2018-12-18 | Abbott Cardiovascular Systems Inc. | Substituted polycaprolactone for coating |
US9737638B2 (en) * | 2007-06-20 | 2017-08-22 | Abbott Cardiovascular Systems, Inc. | Polyester amide copolymers having free carboxylic acid pendant groups |
US7927621B2 (en) * | 2007-06-25 | 2011-04-19 | Abbott Cardiovascular Systems Inc. | Thioester-ester-amide copolymers |
US20090004243A1 (en) | 2007-06-29 | 2009-01-01 | Pacetti Stephen D | Biodegradable triblock copolymers for implantable devices |
US8689728B2 (en) * | 2007-10-05 | 2014-04-08 | Menendez Adolfo | Apparatus for holding a medical device during coating |
US20090093870A1 (en) * | 2007-10-05 | 2009-04-09 | Bacoustics, Llc | Method for Holding a Medical Device During Coating |
US9814553B1 (en) | 2007-10-10 | 2017-11-14 | Abbott Cardiovascular Systems Inc. | Bioabsorbable semi-crystalline polymer for controlling release of drug from a coating |
US20090306120A1 (en) * | 2007-10-23 | 2009-12-10 | Florencia Lim | Terpolymers containing lactide and glycolide |
US20090104241A1 (en) * | 2007-10-23 | 2009-04-23 | Pacetti Stephen D | Random amorphous terpolymer containing lactide and glycolide |
US20090110713A1 (en) * | 2007-10-31 | 2009-04-30 | Florencia Lim | Biodegradable polymeric materials providing controlled release of hydrophobic drugs from implantable devices |
US8642062B2 (en) | 2007-10-31 | 2014-02-04 | Abbott Cardiovascular Systems Inc. | Implantable device having a slow dissolving polymer |
US8128983B2 (en) * | 2008-04-11 | 2012-03-06 | Abbott Cardiovascular Systems Inc. | Coating comprising poly(ethylene glycol)-poly(lactide-glycolide-caprolactone) interpenetrating network |
US8916188B2 (en) * | 2008-04-18 | 2014-12-23 | Abbott Cardiovascular Systems Inc. | Block copolymer comprising at least one polyester block and a poly (ethylene glycol) block |
US20090297584A1 (en) * | 2008-04-18 | 2009-12-03 | Florencia Lim | Biosoluble coating with linear over time mass loss |
US8697113B2 (en) * | 2008-05-21 | 2014-04-15 | Abbott Cardiovascular Systems Inc. | Coating comprising a terpolymer comprising caprolactone and glycolide |
US8697110B2 (en) * | 2009-05-14 | 2014-04-15 | Abbott Cardiovascular Systems Inc. | Polymers comprising amorphous terpolymers and semicrystalline blocks |
US9309347B2 (en) | 2009-05-20 | 2016-04-12 | Biomedical, Inc. | Bioresorbable thermoset polyester/urethane elastomers |
US8888840B2 (en) * | 2009-05-20 | 2014-11-18 | Boston Scientific Scimed, Inc. | Drug eluting medical implant |
US20110319987A1 (en) | 2009-05-20 | 2011-12-29 | Arsenal Medical | Medical implant |
WO2010135433A1 (en) * | 2009-05-20 | 2010-11-25 | Arsenal Medical, Inc. | Medical implant |
US9265633B2 (en) | 2009-05-20 | 2016-02-23 | 480 Biomedical, Inc. | Drug-eluting medical implants |
US8992601B2 (en) | 2009-05-20 | 2015-03-31 | 480 Biomedical, Inc. | Medical implants |
US8429831B2 (en) | 2009-09-04 | 2013-04-30 | Abbott Cardiovascular Systems Inc. | Drug-eluting coatings applied to medical devices by spraying and drying to remove solvent |
US8573148B2 (en) * | 2009-09-04 | 2013-11-05 | Abbott Cardiovascular Systems Inc. | System for coating a stent |
US8313791B2 (en) | 2010-04-01 | 2012-11-20 | Abbott Cardiovascular Systems Inc. | Mandrels supporting medical devices during processing of the medical devices |
US9126366B2 (en) * | 2011-06-15 | 2015-09-08 | Korea Institute Of Machinery & Materials | Apparatus and method for manufacturing cell culture scaffold |
US9909807B2 (en) | 2011-09-16 | 2018-03-06 | Abbott Cardiovascular Systems Inc. | Dryers for removing solvent from a drug-eluting coating applied to medical devices |
US9545301B2 (en) | 2013-03-15 | 2017-01-17 | Covidien Lp | Coated medical devices and methods of making and using same |
US9320592B2 (en) | 2013-03-15 | 2016-04-26 | Covidien Lp | Coated medical devices and methods of making and using same |
US9668890B2 (en) | 2013-11-22 | 2017-06-06 | Covidien Lp | Anti-thrombogenic medical devices and methods |
US9789228B2 (en) | 2014-12-11 | 2017-10-17 | Covidien Lp | Antimicrobial coatings for medical devices and processes for preparing such coatings |
CN110976189B (en) * | 2019-12-19 | 2021-06-22 | 张存存 | Auxiliary dispensing equipment for assembling ternary battery |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1133334A (en) * | 1912-06-18 | 1915-03-30 | Detroit Dental Mfg Company | Work-holding tool. |
US1333334A (en) * | 1918-04-05 | 1920-03-09 | Warren Hines Nesmith | Gin or delinting-gin |
US1346584A (en) * | 1920-04-15 | 1920-07-13 | Edward H Angle | Orthodontic implement |
US3226245A (en) * | 1958-02-05 | 1965-12-28 | Polymer Corp | Coating method and apparatus |
US5716981A (en) * | 1993-07-19 | 1998-02-10 | Angiogenesis Technologies, Inc. | Anti-angiogenic compositions and methods of use |
Family Cites Families (403)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR732895A (en) * | 1932-10-18 | 1932-09-25 | Consortium Elektrochem Ind | Articles spun in polyvinyl alcohol |
US2386454A (en) | 1940-11-22 | 1945-10-09 | Bell Telephone Labor Inc | High molecular weight linear polyester-amides |
US2845346A (en) | 1954-01-13 | 1958-07-29 | Schwarzkopf Dev Co | Method of forming porous cemented metal powder bodies |
US3016875A (en) * | 1958-12-11 | 1962-01-16 | United States Steel Corp | Apparatus for coating pipe |
US3849514A (en) | 1967-11-17 | 1974-11-19 | Eastman Kodak Co | Block polyester-polyamide copolymers |
US3773737A (en) | 1971-06-09 | 1973-11-20 | Sutures Inc | Hydrolyzable polymers of amino acid and hydroxy acids |
BE793124A (en) | 1972-06-23 | 1973-04-16 | Wheeling Pittsburgh Steel Corp | METAL PROTECTIVE TUBES FOR ELECTRICAL PIPES |
US3882816A (en) | 1972-09-22 | 1975-05-13 | Western Electric Co | Apparatus for forming layers of fusible metal on articles |
US3995075A (en) | 1974-04-18 | 1976-11-30 | Continental Can Company, Inc. | Inside stripe by intermittent exterior spray guns |
US4011388A (en) * | 1974-07-02 | 1977-03-08 | E. I. Du Pont De Nemours And Company | Process for preparing emulsions by polymerization of aqueous monomer-polymer dispersions |
US4201149A (en) | 1974-12-17 | 1980-05-06 | Basf Aktiengesellschaft | Apparatus for spin coating in the production of thin magnetic layers for magnetic discs |
US4374669A (en) | 1975-05-09 | 1983-02-22 | Mac Gregor David C | Cardiovascular prosthetic devices and implants with porous systems |
US4082212A (en) | 1976-03-15 | 1978-04-04 | Southwire Company | Galvanized tube welded seam repair metallizing process |
DE2935097A1 (en) | 1978-09-07 | 1980-03-20 | Kuraray Co | AETHYLENE / VINYL ALCOHOL COPOLYMER MEMBRANE |
US4329383A (en) | 1979-07-24 | 1982-05-11 | Nippon Zeon Co., Ltd. | Non-thrombogenic material comprising substrate which has been reacted with heparin |
SU790725A1 (en) | 1979-07-27 | 1983-01-23 | Ордена Ленина Институт Элементоорганических Соединений Ан Ссср | Process for preparing alkylaromatic polyimides |
US4226243A (en) | 1979-07-27 | 1980-10-07 | Ethicon, Inc. | Surgical devices of polyesteramides derived from bis-oxamidodiols and dicarboxylic acids |
US4290383A (en) | 1979-07-31 | 1981-09-22 | Creative Craftsmen, Inc. | Spraying arrangement |
SU872531A1 (en) | 1979-08-07 | 1981-10-15 | Институт Физиологии Им.И.С.Бериташвили Ан Гсср | Method of producing polyurethans |
SU811750A1 (en) | 1979-08-07 | 1983-09-23 | Институт Физиологии Им.С.И.Бериташвили | Bis-bicarbonates of aliphatic diols as monomers for preparing polyurethanes and process for producing the same |
SU876663A1 (en) | 1979-11-11 | 1981-10-30 | Институт Физиологии Им. Академика И.С.Бериташвили Ан Гсср | Method of producing polyarylates |
US4343931A (en) | 1979-12-17 | 1982-08-10 | Minnesota Mining And Manufacturing Company | Synthetic absorbable surgical devices of poly(esteramides) |
US4529792A (en) | 1979-12-17 | 1985-07-16 | Minnesota Mining And Manufacturing Company | Process for preparing synthetic absorbable poly(esteramides) |
SU1016314A1 (en) | 1979-12-17 | 1983-05-07 | Институт Физиологии Им.И.С.Бериташвили | Process for producing polyester urethanes |
SU905228A1 (en) | 1980-03-06 | 1982-02-15 | Институт Физиологии Им. Акад.И.С. Бериташвили Ан Гсср | Method for preparing thiourea |
US4629563B1 (en) | 1980-03-14 | 1997-06-03 | Memtec North America | Asymmetric membranes |
US4489670A (en) | 1983-05-16 | 1984-12-25 | Sermetel | Fixture for centrifugal apparatus |
US4560374A (en) | 1983-10-17 | 1985-12-24 | Hammerslag Julius G | Method for repairing stenotic vessels |
JPS6174668A (en) | 1984-09-19 | 1986-04-16 | Yoshida Kogyo Kk <Ykk> | Device for supplying separate paint in rotary painting machine |
US4640846A (en) * | 1984-09-25 | 1987-02-03 | Yue Kuo | Semiconductor spin coating method |
SU1293518A1 (en) | 1985-04-11 | 1987-02-28 | Тбилисский зональный научно-исследовательский и проектный институт типового и экспериментального проектирования жилых и общественных зданий | Installation for testing specimen of cross-shaped structure |
JPS61276561A (en) | 1985-05-31 | 1986-12-06 | 株式会社クラレ | Blood treatment apparatus |
US4656242A (en) | 1985-06-07 | 1987-04-07 | Henkel Corporation | Poly(ester-amide) compositions |
SE459005B (en) | 1985-07-12 | 1989-05-29 | Aake Rikard Lindahl | SET TO MANUFACTURE SPHERICAL POLYMER PARTICLES |
US4733665C2 (en) | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US4611051A (en) | 1985-12-31 | 1986-09-09 | Union Camp Corporation | Novel poly(ester-amide) hot-melt adhesives |
JPS6346171A (en) * | 1986-06-06 | 1988-02-27 | 旭光学工業株式会社 | Support of medical device stayed in living body |
US4882168A (en) | 1986-09-05 | 1989-11-21 | American Cyanamid Company | Polyesters containing alkylene oxide blocks as drug delivery systems |
US5017420A (en) | 1986-10-23 | 1991-05-21 | Hoechst Celanese Corp. | Process for preparing electrically conductive shaped articles from polybenzimidazoles |
JPH0696023B2 (en) | 1986-11-10 | 1994-11-30 | 宇部日東化成株式会社 | Artificial blood vessel and method for producing the same |
US4762128A (en) | 1986-12-09 | 1988-08-09 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
US4893623A (en) * | 1986-12-09 | 1990-01-16 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
IT1196836B (en) | 1986-12-12 | 1988-11-25 | Sorin Biomedica Spa | Polymeric or metal alloy prosthesis with biocompatible carbon coating |
US5721131A (en) * | 1987-03-06 | 1998-02-24 | United States Of America As Represented By The Secretary Of The Navy | Surface modification of polymers with self-assembled monolayers that promote adhesion, outgrowth and differentiation of biological cells |
US4800882A (en) | 1987-03-13 | 1989-01-31 | Cook Incorporated | Endovascular stent and delivery system |
JPS63238872A (en) | 1987-03-25 | 1988-10-04 | テルモ株式会社 | Instrument for securing inner diameter of cavity of tubular organ and catheter equipped therewith |
US6387379B1 (en) | 1987-04-10 | 2002-05-14 | University Of Florida | Biofunctional surface modified ocular implants, surgical instruments, medical devices, prostheses, contact lenses and the like |
US5059211A (en) | 1987-06-25 | 1991-10-22 | Duke University | Absorbable vascular stent |
US5527337A (en) | 1987-06-25 | 1996-06-18 | Duke University | Bioabsorbable stent and method of making the same |
US4894231A (en) | 1987-07-28 | 1990-01-16 | Biomeasure, Inc. | Therapeutic agent delivery system |
US4886062A (en) | 1987-10-19 | 1989-12-12 | Medtronic, Inc. | Intravascular radially expandable stent and method of implant |
US4906423A (en) | 1987-10-23 | 1990-03-06 | Dow Corning Wright | Methods for forming porous-surfaced polymeric bodies |
US5019096A (en) | 1988-02-11 | 1991-05-28 | Trustees Of Columbia University In The City Of New York | Infection-resistant compositions, medical devices and surfaces and methods for preparing and using same |
JP2561309B2 (en) | 1988-03-28 | 1996-12-04 | テルモ株式会社 | Medical material and manufacturing method thereof |
US4865879A (en) | 1988-03-31 | 1989-09-12 | Gordon Finlay | Method for restoring and reinforcing wooden structural component |
US4931287A (en) | 1988-06-14 | 1990-06-05 | University Of Utah | Heterogeneous interpenetrating polymer networks for the controlled release of drugs |
US5328471A (en) | 1990-02-26 | 1994-07-12 | Endoluminal Therapeutics, Inc. | Method and apparatus for treatment of focal disease in hollow tubular organs and other tissue lumens |
US4846791A (en) | 1988-09-02 | 1989-07-11 | Advanced Medical Technology & Development Corp. | Multi-lumen catheter |
US4977901A (en) | 1988-11-23 | 1990-12-18 | Minnesota Mining And Manufacturing Company | Article having non-crosslinked crystallized polymer coatings |
US5584433A (en) | 1991-08-22 | 1996-12-17 | Nakagawa; Mitsuyoshi | Atomization method and atomizer |
US5201314A (en) | 1989-03-09 | 1993-04-13 | Vance Products Incorporated | Echogenic devices, material and method |
US4992312A (en) * | 1989-03-13 | 1991-02-12 | Dow Corning Wright Corporation | Methods of forming permeation-resistant, silicone elastomer-containing composite laminates and devices produced thereby |
JP3133750B2 (en) | 1989-03-24 | 2001-02-13 | キヤノン株式会社 | Ink jet cartridge and ink jet recording apparatus using the same |
US4976736A (en) | 1989-04-28 | 1990-12-11 | Interpore International | Coated biomaterials and methods for making same |
JPH0666255B2 (en) * | 1989-05-02 | 1994-08-24 | 三菱電機株式会社 | Spin coating apparatus and method |
US5264246A (en) | 1989-05-02 | 1993-11-23 | Mitsubishi Denki Kabushiki Kaisha | Spin coating method |
IL90193A (en) | 1989-05-04 | 1993-02-21 | Biomedical Polymers Int | Polurethane-based polymeric materials and biomedical articles and pharmaceutical compositions utilizing the same |
US4955899A (en) | 1989-05-26 | 1990-09-11 | Impra, Inc. | Longitudinally compliant vascular graft |
US5037392A (en) | 1989-06-06 | 1991-08-06 | Cordis Corporation | Stent-implanting balloon assembly |
US5272012A (en) | 1989-06-23 | 1993-12-21 | C. R. Bard, Inc. | Medical apparatus having protective, lubricious coating |
JP3031924B2 (en) | 1989-07-07 | 2000-04-10 | フロイント産業株式会社 | Granulation coating equipment |
US5458683A (en) | 1989-07-17 | 1995-10-17 | Crc-Evans Rehabilitation Systems, Inc. | Device for surface cleaning, surface preparation and coating applications |
US5971954A (en) | 1990-01-10 | 1999-10-26 | Rochester Medical Corporation | Method of making catheter |
AU651084B2 (en) | 1990-01-30 | 1994-07-14 | Akzo N.V. | Article for the controlled delivery of an active substance, comprising a hollow space fully enclosed by a wall and filled in full or in part with one or more active substances |
US5242399A (en) | 1990-04-25 | 1993-09-07 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5298260A (en) * | 1990-05-01 | 1994-03-29 | Mediventures, Inc. | Topical drug delivery with polyoxyalkylene polymer thermoreversible gels adjustable for pH and osmolality |
US5292516A (en) * | 1990-05-01 | 1994-03-08 | Mediventures, Inc. | Body cavity drug delivery with thermoreversible gels containing polyoxyalkylene copolymers |
US5306501A (en) | 1990-05-01 | 1994-04-26 | Mediventures, Inc. | Drug delivery by injection with thermoreversible gels containing polyoxyalkylene copolymers |
US5300295A (en) | 1990-05-01 | 1994-04-05 | Mediventures, Inc. | Ophthalmic drug delivery with thermoreversible polyoxyalkylene gels adjustable for pH |
WO1991017724A1 (en) | 1990-05-17 | 1991-11-28 | Harbor Medical Devices, Inc. | Medical device polymer |
CA2038605C (en) | 1990-06-15 | 2000-06-27 | Leonard Pinchuk | Crack-resistant polycarbonate urethane polymer prostheses and the like |
US6060451A (en) | 1990-06-15 | 2000-05-09 | The National Research Council Of Canada | Thrombin inhibitors based on the amino acid sequence of hirudin |
AU8074591A (en) | 1990-06-15 | 1992-01-07 | Cortrak Medical, Inc. | Drug delivery apparatus and method |
US5112457A (en) | 1990-07-23 | 1992-05-12 | Case Western Reserve University | Process for producing hydroxylated plasma-polymerized films and the use of the films for enhancing the compatiblity of biomedical implants |
US5455040A (en) | 1990-07-26 | 1995-10-03 | Case Western Reserve University | Anticoagulant plasma polymer-modified substrate |
US5258020A (en) | 1990-09-14 | 1993-11-02 | Michael Froix | Method of using expandable polymeric stent with memory |
US6248129B1 (en) | 1990-09-14 | 2001-06-19 | Quanam Medical Corporation | Expandable polymeric stent with memory and delivery apparatus and method |
US5163952A (en) | 1990-09-14 | 1992-11-17 | Michael Froix | Expandable polymeric stent with memory and delivery apparatus and method |
US5462990A (en) | 1990-10-15 | 1995-10-31 | Board Of Regents, The University Of Texas System | Multifunctional organic polymers |
GB9027793D0 (en) | 1990-12-21 | 1991-02-13 | Ucb Sa | Polyester-amides containing terminal carboxyl groups |
US5171445A (en) | 1991-03-26 | 1992-12-15 | Memtec America Corporation | Ultraporous and microporous membranes and method of making membranes |
US5188734A (en) * | 1991-03-26 | 1993-02-23 | Memtec America Corporation | Ultraporous and microporous integral membranes |
US5330768A (en) | 1991-07-05 | 1994-07-19 | Massachusetts Institute Of Technology | Controlled drug delivery using polymer/pluronic blends |
WO1993004720A1 (en) | 1991-09-12 | 1993-03-18 | THE UNITED STATES, as represented by SECRETARY DEPARTMENT OF HEALTH AND HUMAN SERVICES | Apparatus for and method of making ultra thin walled wire reinforced endotracheal tubing and product thereof |
US5229045A (en) | 1991-09-18 | 1993-07-20 | Kontron Instruments Inc. | Process for making porous membranes |
US5500013A (en) | 1991-10-04 | 1996-03-19 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
US5234457A (en) | 1991-10-09 | 1993-08-10 | Boston Scientific Corporation | Impregnated stent |
CA2079417C (en) * | 1991-10-28 | 2003-01-07 | Lilip Lau | Expandable stents and method of making same |
US5573934A (en) * | 1992-04-20 | 1996-11-12 | Board Of Regents, The University Of Texas System | Gels for encapsulation of biological materials |
US5282823A (en) | 1992-03-19 | 1994-02-01 | Medtronic, Inc. | Intravascular radially expandable stent |
US5599352A (en) | 1992-03-19 | 1997-02-04 | Medtronic, Inc. | Method of making a drug eluting stent |
GB9206736D0 (en) | 1992-03-27 | 1992-05-13 | Sandoz Ltd | Improvements of organic compounds and their use in pharmaceutical compositions |
US5219980A (en) | 1992-04-16 | 1993-06-15 | Sri International | Polymers biodegradable or bioerodiable into amino acids |
DE69325845T2 (en) | 1992-04-28 | 2000-01-05 | Terumo Corp | Thermoplastic polymer composition and medical devices made therefrom |
US5358740A (en) | 1992-06-24 | 1994-10-25 | Massachusetts Institute Of Technology | Method for low pressure spin coating and low pressure spin coating apparatus |
DE4224401A1 (en) | 1992-07-21 | 1994-01-27 | Pharmatech Gmbh | New biodegradable homo- and co-polymer(s) for pharmaceutical use - produced by polycondensation of prod. from heterolytic cleavage of aliphatic polyester with functionalised (cyclo)aliphatic cpd. |
US5342621A (en) | 1992-09-15 | 1994-08-30 | Advanced Cardiovascular Systems, Inc. | Antithrombogenic surface |
FR2699168B1 (en) | 1992-12-11 | 1995-01-13 | Rhone Poulenc Chimie | Method of treating a material comprising a polymer by hydrolysis. |
DE4242476C1 (en) | 1992-12-16 | 1994-08-11 | Eppendorf Geraetebau Netheler | Device for centrifuging samples |
EP0604022A1 (en) | 1992-12-22 | 1994-06-29 | Advanced Cardiovascular Systems, Inc. | Multilayered biodegradable stent and method for its manufacture |
WO1994021320A1 (en) * | 1993-03-15 | 1994-09-29 | Advanced Cardiovascular Systems, Inc. | Fluid delivery catheter |
US5378511A (en) * | 1993-03-22 | 1995-01-03 | International Business Machines Corporation | Material-saving resist spinner and process |
US5308338A (en) | 1993-04-22 | 1994-05-03 | Helfrich G Baird | Catheter or the like with medication injector to prevent infection |
US20020055710A1 (en) | 1998-04-30 | 2002-05-09 | Ronald J. Tuch | Medical device for delivering a therapeutic agent and method of preparation |
US5824048A (en) | 1993-04-26 | 1998-10-20 | Medtronic, Inc. | Method for delivering a therapeutic substance to a body lumen |
US5464650A (en) | 1993-04-26 | 1995-11-07 | Medtronic, Inc. | Intravascular stent and method |
IT1276342B1 (en) | 1993-06-04 | 1997-10-30 | Ist Naz Stud Cura Dei Tumori | METAL STENT COVERED WITH BIOCOMPATIBLE POLYMERIC MATERIAL |
JPH0767895A (en) | 1993-06-25 | 1995-03-14 | Sumitomo Electric Ind Ltd | Antimicrobial artificial blood vessel and suture yarn for antimicrobial operation |
EG20321A (en) | 1993-07-21 | 1998-10-31 | Otsuka Pharma Co Ltd | Medical material and process for producing the same |
DE4327024A1 (en) | 1993-08-12 | 1995-02-16 | Bayer Ag | Thermoplastically processable and biodegradable aliphatic polyesteramides |
US5380299A (en) * | 1993-08-30 | 1995-01-10 | Med Institute, Inc. | Thrombolytic treated intravascular medical device |
US5578048A (en) | 1993-09-15 | 1996-11-26 | United States Surgical Corporation | Manipulator apparatus |
WO1995010989A1 (en) | 1993-10-19 | 1995-04-27 | Scimed Life Systems, Inc. | Intravascular stent pump |
US5723004A (en) | 1993-10-21 | 1998-03-03 | Corvita Corporation | Expandable supportive endoluminal grafts |
US5855598A (en) * | 1993-10-21 | 1999-01-05 | Corvita Corporation | Expandable supportive branched endoluminal grafts |
JP3758048B2 (en) | 1993-10-26 | 2006-03-22 | 帝国ピストンリング株式会社 | Ring coating method and coating device |
JP2703510B2 (en) | 1993-12-28 | 1998-01-26 | アドヴァンスド カーディオヴァスキュラー システムズ インコーポレーテッド | Expandable stent and method of manufacturing the same |
EP0741585A1 (en) | 1994-01-21 | 1996-11-13 | Brown University Research Foundation | Biocompatible implants |
US6051576A (en) | 1994-01-28 | 2000-04-18 | University Of Kentucky Research Foundation | Means to achieve sustained release of synergistic drugs by conjugation |
WO1995024929A2 (en) | 1994-03-15 | 1995-09-21 | Brown University Research Foundation | Polymeric gene delivery system |
US5656082A (en) | 1994-04-04 | 1997-08-12 | Tatsumo Kabushiki Kaisha | Liquid applying apparatus utilizing centrifugal force |
US5567410A (en) | 1994-06-24 | 1996-10-22 | The General Hospital Corporation | Composotions and methods for radiographic imaging |
US5629077A (en) | 1994-06-27 | 1997-05-13 | Advanced Cardiovascular Systems, Inc. | Biodegradable mesh and film stent |
US5670558A (en) | 1994-07-07 | 1997-09-23 | Terumo Kabushiki Kaisha | Medical instruments that exhibit surface lubricity when wetted |
US5788979A (en) | 1994-07-22 | 1998-08-04 | Inflow Dynamics Inc. | Biodegradable coating with inhibitory properties for application to biocompatible materials |
US5516881A (en) | 1994-08-10 | 1996-05-14 | Cornell Research Foundation, Inc. | Aminoxyl-containing radical spin labeling in polymers and copolymers |
US5891108A (en) | 1994-09-12 | 1999-04-06 | Cordis Corporation | Drug delivery stent |
US5578073A (en) | 1994-09-16 | 1996-11-26 | Ramot Of Tel Aviv University | Thromboresistant surface treatment for biomaterials |
US5558900A (en) | 1994-09-22 | 1996-09-24 | Fan; You-Ling | One-step thromboresistant, lubricious coating |
US5649977A (en) | 1994-09-22 | 1997-07-22 | Advanced Cardiovascular Systems, Inc. | Metal reinforced polymer stent |
US5485496A (en) * | 1994-09-22 | 1996-01-16 | Cornell Research Foundation, Inc. | Gamma irradiation sterilizing of biomaterial medical devices or products, with improved degradation and mechanical properties |
FR2724938A1 (en) | 1994-09-28 | 1996-03-29 | Lvmh Rech | POLYMERS FUNCTIONALIZED BY AMINO ACIDS OR AMINO ACID DERIVATIVES, THEIR USE AS SURFACTANTS, IN PARTICULAR, IN COSMETIC COMPOSITIONS AND IN PARTICULAR NAIL POLISH. |
ES2155534T3 (en) * | 1994-10-12 | 2001-05-16 | Focal Inc | ADMINISTRATION DIRECTED THROUGH BIODEGRADABLE POLYMERS. |
US5643580A (en) | 1994-10-17 | 1997-07-01 | Surface Genesis, Inc. | Biocompatible coating, medical device using the same and methods |
US5836965A (en) | 1994-10-19 | 1998-11-17 | Jendersee; Brad | Stent delivery and deployment method |
US5707385A (en) * | 1994-11-16 | 1998-01-13 | Advanced Cardiovascular Systems, Inc. | Drug loaded elastic membrane and method for delivery |
US5637113A (en) | 1994-12-13 | 1997-06-10 | Advanced Cardiovascular Systems, Inc. | Polymer film for wrapping a stent structure |
US5569198A (en) | 1995-01-23 | 1996-10-29 | Cortrak Medical Inc. | Microporous catheter |
US6017577A (en) | 1995-02-01 | 2000-01-25 | Schneider (Usa) Inc. | Slippery, tenaciously adhering hydrophilic polyurethane hydrogel coatings, coated polymer substrate materials, and coated medical devices |
US5919570A (en) | 1995-02-01 | 1999-07-06 | Schneider Inc. | Slippery, tenaciously adhering hydrogel coatings containing a polyurethane-urea polymer hydrogel commingled with a poly(N-vinylpyrrolidone) polymer hydrogel, coated polymer and metal substrate materials, and coated medical devices |
US5869127A (en) * | 1995-02-22 | 1999-02-09 | Boston Scientific Corporation | Method of providing a substrate with a bio-active/biocompatible coating |
US6231600B1 (en) | 1995-02-22 | 2001-05-15 | Scimed Life Systems, Inc. | Stents with hybrid coating for medical devices |
US5702754A (en) | 1995-02-22 | 1997-12-30 | Meadox Medicals, Inc. | Method of providing a substrate with a hydrophilic coating and substrates, particularly medical devices, provided with such coatings |
US5854376A (en) | 1995-03-09 | 1998-12-29 | Sekisui Kaseihin Kogyo Kabushiki Kaisha | Aliphatic ester-amide copolymer resins |
US5605696A (en) * | 1995-03-30 | 1997-02-25 | Advanced Cardiovascular Systems, Inc. | Drug loaded polymeric material and method of manufacture |
WO1996033233A1 (en) | 1995-04-19 | 1996-10-24 | Kazunori Kataoka | Heterotelechelic block copolymers and process for producing the same |
US6120536A (en) | 1995-04-19 | 2000-09-19 | Schneider (Usa) Inc. | Medical devices with long term non-thrombogenic coatings |
US6099562A (en) | 1996-06-13 | 2000-08-08 | Schneider (Usa) Inc. | Drug coating with topcoat |
US5837313A (en) * | 1995-04-19 | 1998-11-17 | Schneider (Usa) Inc | Drug release stent coating process |
US20020091433A1 (en) | 1995-04-19 | 2002-07-11 | Ni Ding | Drug release coated stent |
US5628786A (en) | 1995-05-12 | 1997-05-13 | Impra, Inc. | Radially expandable vascular graft with resistance to longitudinal compression and method of making same |
US5674242A (en) | 1995-06-06 | 1997-10-07 | Quanam Medical Corporation | Endoprosthetic device with therapeutic compound |
US7550005B2 (en) * | 1995-06-07 | 2009-06-23 | Cook Incorporated | Coated implantable medical device |
US6129761A (en) | 1995-06-07 | 2000-10-10 | Reprogenesis, Inc. | Injectable hydrogel compositions |
US6010530A (en) * | 1995-06-07 | 2000-01-04 | Boston Scientific Technology, Inc. | Self-expanding endoluminal prosthesis |
US7611533B2 (en) * | 1995-06-07 | 2009-11-03 | Cook Incorporated | Coated implantable medical device |
US5820917A (en) | 1995-06-07 | 1998-10-13 | Medtronic, Inc. | Blood-contacting medical device and method |
US5609629A (en) * | 1995-06-07 | 1997-03-11 | Med Institute, Inc. | Coated implantable medical device |
CA2178541C (en) | 1995-06-07 | 2009-11-24 | Neal E. Fearnot | Implantable medical device |
US6774278B1 (en) * | 1995-06-07 | 2004-08-10 | Cook Incorporated | Coated implantable medical device |
CH690857A5 (en) * | 1995-07-04 | 2001-02-15 | Erich Bergmann | System for plasma-enhanced physical Hochvakuumbedampfung workpieces with wear-resistant coatings and methods for performing in this complex |
US5667767A (en) | 1995-07-27 | 1997-09-16 | Micro Therapeutics, Inc. | Compositions for use in embolizing blood vessels |
US5877224A (en) * | 1995-07-28 | 1999-03-02 | Rutgers, The State University Of New Jersey | Polymeric drug formulations |
US5935135A (en) | 1995-09-29 | 1999-08-10 | United States Surgical Corporation | Balloon delivery system for deploying stents |
US5723219A (en) | 1995-12-19 | 1998-03-03 | Talison Research | Plasma deposited film networks |
US5607442A (en) * | 1995-11-13 | 1997-03-04 | Isostent, Inc. | Stent with improved radiopacity and appearance characteristics |
US5788626A (en) | 1995-11-21 | 1998-08-04 | Schneider (Usa) Inc | Method of making a stent-graft covered with expanded polytetrafluoroethylene |
US5658995A (en) | 1995-11-27 | 1997-08-19 | Rutgers, The State University | Copolymers of tyrosine-based polycarbonate and poly(alkylene oxide) |
DE19545678A1 (en) | 1995-12-07 | 1997-06-12 | Goldschmidt Ag Th | Copolymers of polyamino acid esters |
AU717660B2 (en) | 1995-12-18 | 2000-03-30 | Angiodevice International Gmbh | Crosslinked polymer compositions and methods for their use |
US6203569B1 (en) * | 1996-01-04 | 2001-03-20 | Bandula Wijay | Flexible stent |
US6033582A (en) * | 1996-01-22 | 2000-03-07 | Etex Corporation | Surface modification of medical implants |
US6054553A (en) | 1996-01-29 | 2000-04-25 | Bayer Ag | Process for the preparation of polymers having recurring agents |
US5772864A (en) | 1996-02-23 | 1998-06-30 | Meadox Medicals, Inc. | Method for manufacturing implantable medical devices |
US5823996A (en) | 1996-02-29 | 1998-10-20 | Cordis Corporation | Infusion balloon catheter |
CA2199890C (en) | 1996-03-26 | 2002-02-05 | Leonard Pinchuk | Stents and stent-grafts having enhanced hoop strength and methods of making the same |
US5713949A (en) * | 1996-08-06 | 1998-02-03 | Jayaraman; Swaminathan | Microporous covered stents and method of coating |
US5932299A (en) | 1996-04-23 | 1999-08-03 | Katoot; Mohammad W. | Method for modifying the surface of an object |
US5955509A (en) | 1996-05-01 | 1999-09-21 | Board Of Regents, The University Of Texas System | pH dependent polymer micelles |
US5610241A (en) * | 1996-05-07 | 1997-03-11 | Cornell Research Foundation, Inc. | Reactive graft polymer with biodegradable polymer backbone and method for preparing reactive biodegradable polymers |
US6440221B2 (en) | 1996-05-13 | 2002-08-27 | Applied Materials, Inc. | Process chamber having improved temperature control |
US6248398B1 (en) | 1996-05-22 | 2001-06-19 | Applied Materials, Inc. | Coater having a controllable pressurized process chamber for semiconductor processing |
US5876433A (en) * | 1996-05-29 | 1999-03-02 | Ethicon, Inc. | Stent and method of varying amounts of heparin coated thereon to control treatment |
US5874165A (en) | 1996-06-03 | 1999-02-23 | Gore Enterprise Holdings, Inc. | Materials and method for the immobilization of bioactive species onto polymeric subtrates |
NL1003459C2 (en) * | 1996-06-28 | 1998-01-07 | Univ Twente | Copoly (ester amides) and copoly (ester urethanes). |
US5928279A (en) | 1996-07-03 | 1999-07-27 | Baxter International Inc. | Stented, radially expandable, tubular PTFE grafts |
US5833659A (en) | 1996-07-10 | 1998-11-10 | Cordis Corporation | Infusion balloon catheter |
US5711958A (en) | 1996-07-11 | 1998-01-27 | Life Medical Sciences, Inc. | Methods for reducing or eliminating post-surgical adhesion formation |
US5741554A (en) | 1996-07-26 | 1998-04-21 | Bio Dot, Inc. | Method of dispensing a liquid reagent |
US5830178A (en) | 1996-10-11 | 1998-11-03 | Micro Therapeutics, Inc. | Methods for embolizing vascular sites with an emboilizing composition comprising dimethylsulfoxide |
US6060518A (en) | 1996-08-16 | 2000-05-09 | Supratek Pharma Inc. | Polymer compositions for chemotherapy and methods of treatment using the same |
US6174329B1 (en) * | 1996-08-22 | 2001-01-16 | Advanced Cardiovascular Systems, Inc. | Protective coating for a stent with intermediate radiopaque coating |
US5980530A (en) | 1996-08-23 | 1999-11-09 | Scimed Life Systems Inc | Stent delivery system |
WO1998007523A1 (en) * | 1996-08-23 | 1998-02-26 | Pursley Matt D | Apparatus and method for nonextrusion manufacturing of catheters |
US5911752A (en) | 1996-09-13 | 1999-06-15 | Intratherapeutics, Inc. | Method for collapsing a stent |
US6306165B1 (en) | 1996-09-13 | 2001-10-23 | Meadox Medicals | ePTFE small caliber vascular grafts with significant patency enhancement via a surface coating which contains covalently bonded heparin |
US5783657A (en) | 1996-10-18 | 1998-07-21 | Union Camp Corporation | Ester-terminated polyamides of polymerized fatty acids useful in formulating transparent gels in low polarity liquids |
US6244575B1 (en) | 1996-10-02 | 2001-06-12 | Micron Technology, Inc. | Method and apparatus for vaporizing liquid precursors and system for using same |
US6530951B1 (en) | 1996-10-24 | 2003-03-11 | Cook Incorporated | Silver implantable medical device |
US6197013B1 (en) * | 1996-11-06 | 2001-03-06 | Setagon, Inc. | Method and apparatus for drug and gene delivery |
US6261320B1 (en) | 1996-11-21 | 2001-07-17 | Radiance Medical Systems, Inc. | Radioactive vascular liner |
ZA9710342B (en) | 1996-11-25 | 1998-06-10 | Alza Corp | Directional drug delivery stent and method of use. |
US6120491A (en) | 1997-11-07 | 2000-09-19 | The State University Rutgers | Biodegradable, anionic polymers derived from the amino acid L-tyrosine |
CA2272097C (en) | 1996-12-10 | 2007-02-20 | Purdue Research Foundation | Artificial vascular valves |
US6045899A (en) | 1996-12-12 | 2000-04-04 | Usf Filtration & Separations Group, Inc. | Highly assymetric, hydrophilic, microfiltration membranes having large pore diameters |
US5980972A (en) | 1996-12-20 | 1999-11-09 | Schneider (Usa) Inc | Method of applying drug-release coatings |
US5997517A (en) | 1997-01-27 | 1999-12-07 | Sts Biopolymers, Inc. | Bonding layers for medical device surface coatings |
CA2278613A1 (en) | 1997-01-28 | 1998-07-30 | United States Surgical Corporation | Polyesteramide, its preparation and surgical devices fabricated therefrom |
CA2278606C (en) | 1997-01-28 | 2006-06-20 | United States Surgical Corporation | Polyesteramide, its preparation and surgical devices fabricated therefrom |
ES2229475T3 (en) | 1997-01-28 | 2005-04-16 | United States Surgical Corporation | MOLDED SURGICAL DEVICE MANUFACTURED FROM POLYESTERAMIDS WITH GROUPS DERIVED FROM AMINO ACIDS WHICH ALTERNATE WITH GROUPS DERIVED FROM ALFA-HYDROXIACIDES. |
US6140431A (en) | 1997-02-27 | 2000-10-31 | Rohm And Haas Company | Process for preparing continuously variable-composition copolymers |
US5843172A (en) | 1997-04-15 | 1998-12-01 | Advanced Cardiovascular Systems, Inc. | Porous medicated stent |
US6240616B1 (en) | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US6273913B1 (en) | 1997-04-18 | 2001-08-14 | Cordis Corporation | Modified stent useful for delivery of drugs along stent strut |
US5879697A (en) * | 1997-04-30 | 1999-03-09 | Schneider Usa Inc | Drug-releasing coatings for medical devices |
US6159978A (en) * | 1997-05-28 | 2000-12-12 | Aventis Pharmaceuticals Product, Inc. | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6245760B1 (en) | 1997-05-28 | 2001-06-12 | Aventis Pharmaceuticals Products, Inc | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6180632B1 (en) | 1997-05-28 | 2001-01-30 | Aventis Pharmaceuticals Products Inc. | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6056993A (en) | 1997-05-30 | 2000-05-02 | Schneider (Usa) Inc. | Porous protheses and methods for making the same wherein the protheses are formed by spraying water soluble and water insoluble fibers onto a rotating mandrel |
US5902631A (en) | 1997-06-03 | 1999-05-11 | Wang; Lixiao | Lubricity gradient for medical devices |
FR2764794B1 (en) | 1997-06-20 | 1999-11-12 | Nycomed Lab Sa | EXPANDED TUBULAR DEVICE WITH VARIABLE THICKNESS |
US6110483A (en) | 1997-06-23 | 2000-08-29 | Sts Biopolymers, Inc. | Adherent, flexible hydrogel and medicated coatings |
US6194034B1 (en) * | 1997-07-02 | 2001-02-27 | Konica Corporation | Method of coating a substrate wherein the flow rate of the coating solution is changed |
US6211249B1 (en) | 1997-07-11 | 2001-04-03 | Life Medical Sciences, Inc. | Polyester polyether block copolymers |
US5891507A (en) | 1997-07-28 | 1999-04-06 | Iowa-India Investments Company Limited | Process for coating a surface of a metallic stent |
US5980928A (en) | 1997-07-29 | 1999-11-09 | Terry; Paul B. | Implant for preventing conjunctivitis in cattle |
US5855600A (en) * | 1997-08-01 | 1999-01-05 | Inflow Dynamics Inc. | Flexible implantable stent with composite design |
CA2298580A1 (en) * | 1997-08-08 | 1999-02-18 | The Procter & Gamble Company | Laundry detergent compositions with amino acid based polymers to provide appearance and integrity benefits to fabrics laundered therewith |
US5897911A (en) | 1997-08-11 | 1999-04-27 | Advanced Cardiovascular Systems, Inc. | Polymer-coated stent structure |
US6121027A (en) | 1997-08-15 | 2000-09-19 | Surmodics, Inc. | Polybifunctional reagent having a polymeric backbone and photoreactive moieties and bioactive groups |
US6143370A (en) | 1997-08-27 | 2000-11-07 | Northeastern University | Process for producing polymer coatings with various porosities and surface areas |
US5972027A (en) | 1997-09-30 | 1999-10-26 | Scimed Life Systems, Inc | Porous stent drug delivery system |
US6120788A (en) | 1997-10-16 | 2000-09-19 | Bioamide, Inc. | Bioabsorbable triglycolic acid poly(ester-amide)s |
US6273908B1 (en) | 1997-10-24 | 2001-08-14 | Robert Ndondo-Lay | Stents |
US6015541A (en) * | 1997-11-03 | 2000-01-18 | Micro Therapeutics, Inc. | Radioactive embolizing compositions |
EP1032328A1 (en) | 1997-11-25 | 2000-09-06 | Triad Vascular Systems Inc. | Layered endovascular graft |
US6129755A (en) | 1998-01-09 | 2000-10-10 | Nitinol Development Corporation | Intravascular stent having an improved strut configuration |
US6517534B1 (en) * | 1998-02-11 | 2003-02-11 | Cosman Company, Inc. | Peri-urethral ablation |
US6140127A (en) | 1998-02-18 | 2000-10-31 | Cordis Corporation | Method of coating an intravascular stent with an endothelial cell adhesive five amino acid peptide |
EP1056515A1 (en) | 1998-02-19 | 2000-12-06 | Radiance Medical Systems Inc. | Radioactive stent |
US6228072B1 (en) | 1998-02-19 | 2001-05-08 | Percusurge, Inc. | Shaft for medical catheters |
US6110188A (en) | 1998-03-09 | 2000-08-29 | Corvascular, Inc. | Anastomosis method |
US6258371B1 (en) | 1998-04-03 | 2001-07-10 | Medtronic Inc | Method for making biocompatible medical article |
US6235340B1 (en) | 1998-04-10 | 2001-05-22 | Massachusetts Institute Of Technology | Biopolymer-resistant coatings |
US20030040790A1 (en) * | 1998-04-15 | 2003-02-27 | Furst Joseph G. | Stent coating |
US20010029351A1 (en) | 1998-04-16 | 2001-10-11 | Robert Falotico | Drug combinations and delivery devices for the prevention and treatment of vascular disease |
US7658727B1 (en) | 1998-04-20 | 2010-02-09 | Medtronic, Inc | Implantable medical device with enhanced biocompatibility and biostability |
US20020188037A1 (en) | 1999-04-15 | 2002-12-12 | Chudzik Stephen J. | Method and system for providing bioactive agent release coating |
WO1999055396A1 (en) * | 1998-04-27 | 1999-11-04 | Surmodics, Inc. | Bioactive agent release coating |
US6013099A (en) * | 1998-04-29 | 2000-01-11 | Medtronic, Inc. | Medical device for delivering a water-insoluble therapeutic salt or substance |
US6113629A (en) | 1998-05-01 | 2000-09-05 | Micrus Corporation | Hydrogel for the therapeutic treatment of aneurysms |
KR100314496B1 (en) | 1998-05-28 | 2001-11-22 | 윤동진 | Non-thrombogenic heparin derivatives, process for preparation and use thereof |
US6572651B1 (en) | 1998-06-03 | 2003-06-03 | N.V. Bekaert S.A. | Stents with a diamond like coating |
US6106889A (en) | 1998-06-11 | 2000-08-22 | Biocoat Incorporated | Method of selective coating of articles |
US6171334B1 (en) * | 1998-06-17 | 2001-01-09 | Advanced Cardiovascular Systems, Inc. | Expandable stent and method of use |
US6153252A (en) | 1998-06-30 | 2000-11-28 | Ethicon, Inc. | Process for coating stents |
US6010573A (en) | 1998-07-01 | 2000-01-04 | Virginia Commonwealth University | Apparatus and method for endothelial cell seeding/transfection of intravascular stents |
AU5054499A (en) | 1998-07-21 | 2000-02-14 | Biocompatibles Limited | Coating |
EP1105169A1 (en) | 1998-08-20 | 2001-06-13 | Cook Incorporated | Coated implantable medical device |
US6248127B1 (en) | 1998-08-21 | 2001-06-19 | Medtronic Ave, Inc. | Thromboresistant coated medical device |
US6335029B1 (en) * | 1998-08-28 | 2002-01-01 | Scimed Life Systems, Inc. | Polymeric coatings for controlled delivery of active agents |
US6068202A (en) | 1998-09-10 | 2000-05-30 | Precision Valve & Automotion, Inc. | Spraying and dispensing apparatus |
US6011125A (en) * | 1998-09-25 | 2000-01-04 | General Electric Company | Amide modified polyesters |
US6206915B1 (en) * | 1998-09-29 | 2001-03-27 | Medtronic Ave, Inc. | Drug storing and metering stent |
US6245099B1 (en) | 1998-09-30 | 2001-06-12 | Impra, Inc. | Selective adherence of stent-graft coverings, mandrel and method of making stent-graft device |
US6165267A (en) | 1998-10-07 | 2000-12-26 | Sandia Corporation | Spin coating apparatus |
US6407009B1 (en) | 1998-11-12 | 2002-06-18 | Advanced Micro Devices, Inc. | Methods of manufacture of uniform spin-on films |
US6575933B1 (en) | 1998-11-30 | 2003-06-10 | Cryocath Technologies Inc. | Mechanical support for an expandable membrane |
US6358567B2 (en) * | 1998-12-23 | 2002-03-19 | The Regents Of The University Of California | Colloidal spray method for low cost thin coating deposition |
US6120847A (en) | 1999-01-08 | 2000-09-19 | Scimed Life Systems, Inc. | Surface treatment method for stent coating |
US6530950B1 (en) | 1999-01-12 | 2003-03-11 | Quanam Medical Corporation | Intraluminal stent having coaxial polymer member |
US6419692B1 (en) | 1999-02-03 | 2002-07-16 | Scimed Life Systems, Inc. | Surface protection method for stents and balloon catheters for drug delivery |
US6143354A (en) | 1999-02-08 | 2000-11-07 | Medtronic Inc. | One-step method for attachment of biomolecules to substrate surfaces |
US6273910B1 (en) | 1999-03-11 | 2001-08-14 | Advanced Cardiovascular Systems, Inc. | Stent with varying strut geometry |
US6364903B2 (en) | 1999-03-19 | 2002-04-02 | Meadox Medicals, Inc. | Polymer coated stent |
US6059714A (en) | 1999-03-26 | 2000-05-09 | Implant Sciences Corporation | Radioactive medical devices |
US6372283B1 (en) | 1999-04-02 | 2002-04-16 | Medtronic, Inc. | Plasma process for surface modification of pyrolitic carbon |
JP3398936B2 (en) | 1999-04-09 | 2003-04-21 | 日本エー・エス・エム株式会社 | Semiconductor processing equipment |
US6368658B1 (en) | 1999-04-19 | 2002-04-09 | Scimed Life Systems, Inc. | Coating medical devices using air suspension |
US6156373A (en) | 1999-05-03 | 2000-12-05 | Scimed Life Systems, Inc. | Medical device coating methods and devices |
US6258121B1 (en) | 1999-07-02 | 2001-07-10 | Scimed Life Systems, Inc. | Stent coating |
US6283947B1 (en) * | 1999-07-13 | 2001-09-04 | Advanced Cardiovascular Systems, Inc. | Local drug delivery injection catheter |
US6494862B1 (en) | 1999-07-13 | 2002-12-17 | Advanced Cardiovascular Systems, Inc. | Substance delivery apparatus and a method of delivering a therapeutic substance to an anatomical passageway |
US6177523B1 (en) * | 1999-07-14 | 2001-01-23 | Cardiotech International, Inc. | Functionalized polyurethanes |
US6379381B1 (en) | 1999-09-03 | 2002-04-30 | Advanced Cardiovascular Systems, Inc. | Porous prosthesis and a method of depositing substances into the pores |
US20040029952A1 (en) * | 1999-09-03 | 2004-02-12 | Yung-Ming Chen | Ethylene vinyl alcohol composition and coating |
US6713119B2 (en) | 1999-09-03 | 2004-03-30 | Advanced Cardiovascular Systems, Inc. | Biocompatible coating for a prosthesis and a method of forming the same |
US6287628B1 (en) | 1999-09-03 | 2001-09-11 | Advanced Cardiovascular Systems, Inc. | Porous prosthesis and a method of depositing substances into the pores |
US6790228B2 (en) | 1999-12-23 | 2004-09-14 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US6759054B2 (en) | 1999-09-03 | 2004-07-06 | Advanced Cardiovascular Systems, Inc. | Ethylene vinyl alcohol composition and coating |
US6503556B2 (en) * | 2000-12-28 | 2003-01-07 | Advanced Cardiovascular Systems, Inc. | Methods of forming a coating for a prosthesis |
US6749626B1 (en) | 2000-03-31 | 2004-06-15 | Advanced Cardiovascular Systems, Inc. | Actinomycin D for the treatment of vascular disease |
US6503954B1 (en) * | 2000-03-31 | 2003-01-07 | Advanced Cardiovascular Systems, Inc. | Biocompatible carrier containing actinomycin D and a method of forming the same |
US6203551B1 (en) * | 1999-10-04 | 2001-03-20 | Advanced Cardiovascular Systems, Inc. | Chamber for applying therapeutic substances to an implant device |
US6387123B1 (en) * | 1999-10-13 | 2002-05-14 | Advanced Cardiovascular Systems, Inc. | Stent with radiopaque core |
US6331313B1 (en) | 1999-10-22 | 2001-12-18 | Oculex Pharmaceticals, Inc. | Controlled-release biocompatible ocular drug delivery implant devices and methods |
US6521284B1 (en) | 1999-11-03 | 2003-02-18 | Scimed Life Systems, Inc. | Process for impregnating a porous material with a cross-linkable composition |
US6610087B1 (en) | 1999-11-16 | 2003-08-26 | Scimed Life Systems, Inc. | Endoluminal stent having a matched stiffness region and/or a stiffness gradient and methods for providing stent kink resistance |
US6251136B1 (en) | 1999-12-08 | 2001-06-26 | Advanced Cardiovascular Systems, Inc. | Method of layering a three-coated stent using pharmacological and polymeric agents |
US6613432B2 (en) | 1999-12-22 | 2003-09-02 | Biosurface Engineering Technologies, Inc. | Plasma-deposited coatings, devices and methods |
US6908624B2 (en) | 1999-12-23 | 2005-06-21 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US6283949B1 (en) | 1999-12-27 | 2001-09-04 | Advanced Cardiovascular Systems, Inc. | Refillable implantable drug delivery pump |
AU2599501A (en) | 1999-12-29 | 2001-07-09 | Advanced Cardiovascular Systems Inc. | Device and active component for inhibiting formation of thrombus-inflammatory cell matrix |
US6527801B1 (en) | 2000-04-13 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Biodegradable drug delivery material for stent |
US6387118B1 (en) | 2000-04-20 | 2002-05-14 | Scimed Life Systems, Inc. | Non-crimped stent delivery system |
US20020007213A1 (en) * | 2000-05-19 | 2002-01-17 | Robert Falotico | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US20020007215A1 (en) * | 2000-05-19 | 2002-01-17 | Robert Falotico | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US20020007214A1 (en) * | 2000-05-19 | 2002-01-17 | Robert Falotico | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US20020005206A1 (en) * | 2000-05-19 | 2002-01-17 | Robert Falotico | Antiproliferative drug and delivery device |
US6776796B2 (en) | 2000-05-12 | 2004-08-17 | Cordis Corportation | Antiinflammatory drug and delivery device |
US6673385B1 (en) * | 2000-05-31 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Methods for polymeric coatings stents |
US6395326B1 (en) * | 2000-05-31 | 2002-05-28 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for depositing a coating onto a surface of a prosthesis |
US6279368B1 (en) | 2000-06-07 | 2001-08-28 | Endovascular Technologies, Inc. | Nitinol frame heating and setting mandrel |
US6723373B1 (en) | 2000-06-16 | 2004-04-20 | Cordis Corporation | Device and process for coating stents |
US6585765B1 (en) | 2000-06-29 | 2003-07-01 | Advanced Cardiovascular Systems, Inc. | Implantable device having substances impregnated therein and a method of impregnating the same |
US20020077693A1 (en) | 2000-12-19 | 2002-06-20 | Barclay Bruce J. | Covered, coiled drug delivery stent and method |
US6555157B1 (en) | 2000-07-25 | 2003-04-29 | Advanced Cardiovascular Systems, Inc. | Method for coating an implantable device and system for performing the method |
MXPA03000821A (en) * | 2000-07-27 | 2004-03-18 | Univ Rutgers | Therapeutic polyesters and polyamides. |
US6534112B1 (en) | 2000-08-01 | 2003-03-18 | Ams Research Corporation | Semi-automatic coating system methods for coating medical devices |
US6451373B1 (en) | 2000-08-04 | 2002-09-17 | Advanced Cardiovascular Systems, Inc. | Method of forming a therapeutic coating onto a surface of an implantable prosthesis |
US7476523B2 (en) | 2000-08-14 | 2009-01-13 | Surface Logix, Inc. | Method of patterning a surface using a deformable stamp |
US6503538B1 (en) * | 2000-08-30 | 2003-01-07 | Cornell Research Foundation, Inc. | Elastomeric functional biodegradable copolyester amides and copolyester urethanes |
US6585926B1 (en) | 2000-08-31 | 2003-07-01 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a porous balloon |
US6562136B1 (en) | 2000-09-08 | 2003-05-13 | Surmodics, Inc. | Coating apparatus and method |
US6716444B1 (en) | 2000-09-28 | 2004-04-06 | Advanced Cardiovascular Systems, Inc. | Barriers for polymer-coated implantable medical devices and methods for making the same |
US6254632B1 (en) | 2000-09-28 | 2001-07-03 | Advanced Cardiovascular Systems, Inc. | Implantable medical device having protruding surface structures for drug delivery and cover attachment |
US7261735B2 (en) | 2001-05-07 | 2007-08-28 | Cordis Corporation | Local drug delivery devices and methods for maintaining the drug coatings thereon |
US20020051730A1 (en) | 2000-09-29 | 2002-05-02 | Stanko Bodnar | Coated medical devices and sterilization thereof |
US20020111590A1 (en) | 2000-09-29 | 2002-08-15 | Davila Luis A. | Medical devices, drug coatings and methods for maintaining the drug coatings thereon |
US6746773B2 (en) | 2000-09-29 | 2004-06-08 | Ethicon, Inc. | Coatings for medical devices |
US6506437B1 (en) * | 2000-10-17 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Methods of coating an implantable device having depots formed in a surface thereof |
US6558733B1 (en) | 2000-10-26 | 2003-05-06 | Advanced Cardiovascular Systems, Inc. | Method for etching a micropatterned microdepot prosthesis |
US6758859B1 (en) | 2000-10-30 | 2004-07-06 | Kenny L. Dang | Increased drug-loading and reduced stress drug delivery device |
US6824559B2 (en) | 2000-12-22 | 2004-11-30 | Advanced Cardiovascular Systems, Inc. | Ethylene-carboxyl copolymers as drug delivery matrices |
US7077859B2 (en) | 2000-12-22 | 2006-07-18 | Avantec Vascular Corporation | Apparatus and methods for variably controlled substance delivery from implanted prostheses |
US20020082679A1 (en) | 2000-12-22 | 2002-06-27 | Avantec Vascular Corporation | Delivery or therapeutic capable agents |
US6544543B1 (en) | 2000-12-27 | 2003-04-08 | Advanced Cardiovascular Systems, Inc. | Periodic constriction of vessels to treat ischemic tissue |
US6540776B2 (en) | 2000-12-28 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Sheath for a prosthesis and methods of forming the same |
US6663662B2 (en) | 2000-12-28 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Diffusion barrier layer for implantable devices |
US6468298B1 (en) * | 2000-12-28 | 2002-10-22 | Advanced Cardiovascular Systems, Inc. | Gripping delivery system for self-expanding stents and method of using the same |
US20020087123A1 (en) | 2001-01-02 | 2002-07-04 | Hossainy Syed F.A. | Adhesion of heparin-containing coatings to blood-contacting surfaces of medical devices |
US6544223B1 (en) | 2001-01-05 | 2003-04-08 | Advanced Cardiovascular Systems, Inc. | Balloon catheter for delivering therapeutic agents |
US6544582B1 (en) | 2001-01-05 | 2003-04-08 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for coating an implantable device |
US6645195B1 (en) | 2001-01-05 | 2003-11-11 | Advanced Cardiovascular Systems, Inc. | Intraventricularly guided agent delivery system and method of use |
US20030215564A1 (en) | 2001-01-18 | 2003-11-20 | Heller Phillip F. | Method and apparatus for coating an endoprosthesis |
US6740040B1 (en) | 2001-01-30 | 2004-05-25 | Advanced Cardiovascular Systems, Inc. | Ultrasound energy driven intraventricular catheter to treat ischemia |
US20030032767A1 (en) * | 2001-02-05 | 2003-02-13 | Yasuhiro Tada | High-strength polyester-amide fiber and process for producing the same |
AU2002238076B2 (en) | 2001-02-09 | 2007-05-17 | Endoluminal Therapeutics, Inc. | Endomural therapy |
DE10107795B4 (en) | 2001-02-13 | 2014-05-15 | Berlex Ag | Vascular support with a basic body, method for producing the vascular support, apparatus for coating the vascular support |
US20030004141A1 (en) * | 2001-03-08 | 2003-01-02 | Brown David L. | Medical devices, compositions and methods for treating vulnerable plaque |
US6645135B1 (en) | 2001-03-30 | 2003-11-11 | Advanced Cardiovascular Systems, Inc. | Intravascular catheter device and method for simultaneous local delivery of radiation and a therapeutic substance |
US6623448B2 (en) | 2001-03-30 | 2003-09-23 | Advanced Cardiovascular Systems, Inc. | Steerable drug delivery device |
US6780424B2 (en) | 2001-03-30 | 2004-08-24 | Charles David Claude | Controlled morphologies in polymer drug for release of drugs from polymer films |
US6625486B2 (en) | 2001-04-11 | 2003-09-23 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for intracellular delivery of an agent |
US6764505B1 (en) | 2001-04-12 | 2004-07-20 | Advanced Cardiovascular Systems, Inc. | Variable surface area stent |
US6712845B2 (en) | 2001-04-24 | 2004-03-30 | Advanced Cardiovascular Systems, Inc. | Coating for a stent and a method of forming the same |
AU2002259045B2 (en) * | 2001-04-26 | 2008-05-22 | Psivida Us Inc. | Sustained release drug delivery system containing codrugs |
US6660034B1 (en) | 2001-04-30 | 2003-12-09 | Advanced Cardiovascular Systems, Inc. | Stent for increasing blood flow to ischemic tissues and a method of using the same |
US6656506B1 (en) | 2001-05-09 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Microparticle coated medical device |
US7651695B2 (en) | 2001-05-18 | 2010-01-26 | Advanced Cardiovascular Systems, Inc. | Medicated stents for the treatment of vascular disease |
US6605154B1 (en) * | 2001-05-31 | 2003-08-12 | Advanced Cardiovascular Systems, Inc. | Stent mounting device |
US6743462B1 (en) | 2001-05-31 | 2004-06-01 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating implantable devices |
US7862495B2 (en) | 2001-05-31 | 2011-01-04 | Advanced Cardiovascular Systems, Inc. | Radiation or drug delivery source with activity gradient to minimize edge effects |
US6666880B1 (en) | 2001-06-19 | 2003-12-23 | Advised Cardiovascular Systems, Inc. | Method and system for securing a coated stent to a balloon catheter |
US6695920B1 (en) * | 2001-06-27 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Mandrel for supporting a stent and a method of using the mandrel to coat a stent |
US6572644B1 (en) * | 2001-06-27 | 2003-06-03 | Advanced Cardiovascular Systems, Inc. | Stent mounting device and a method of using the same to coat a stent |
US6673154B1 (en) * | 2001-06-28 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Stent mounting device to coat a stent |
US6565659B1 (en) | 2001-06-28 | 2003-05-20 | Advanced Cardiovascular Systems, Inc. | Stent mounting assembly and a method of using the same to coat a stent |
US6585755B2 (en) | 2001-06-29 | 2003-07-01 | Advanced Cardiovascular | Polymeric stent suitable for imaging by MRI and fluoroscopy |
US6527863B1 (en) | 2001-06-29 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Support device for a stent and a method of using the same to coat a stent |
US6656216B1 (en) | 2001-06-29 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Composite stent with regioselective material |
US6706013B1 (en) | 2001-06-29 | 2004-03-16 | Advanced Cardiovascular Systems, Inc. | Variable length drug delivery catheter |
US6682771B2 (en) * | 2001-07-02 | 2004-01-27 | Scimed Life Systems, Inc. | Coating dispensing system and method using a solenoid head for coating medical devices |
EP1273314A1 (en) | 2001-07-06 | 2003-01-08 | Terumo Kabushiki Kaisha | Stent |
US6641611B2 (en) | 2001-11-26 | 2003-11-04 | Swaminathan Jayaraman | Therapeutic coating for an intravascular implant |
WO2003028590A1 (en) | 2001-09-24 | 2003-04-10 | Medtronic Ave Inc. | Rational drug therapy device and methods |
US7195640B2 (en) * | 2001-09-25 | 2007-03-27 | Cordis Corporation | Coated medical devices for the treatment of vulnerable plaque |
US20030059520A1 (en) * | 2001-09-27 | 2003-03-27 | Yung-Ming Chen | Apparatus for regulating temperature of a composition and a method of coating implantable devices |
US6753071B1 (en) | 2001-09-27 | 2004-06-22 | Advanced Cardiovascular Systems, Inc. | Rate-reducing membrane for release of an agent |
US20030065377A1 (en) | 2001-09-28 | 2003-04-03 | Davila Luis A. | Coated medical devices |
US20030073961A1 (en) | 2001-09-28 | 2003-04-17 | Happ Dorrie M. | Medical device containing light-protected therapeutic agent and a method for fabricating thereof |
US20030088307A1 (en) | 2001-11-05 | 2003-05-08 | Shulze John E. | Potent coatings for stents |
US7585516B2 (en) | 2001-11-12 | 2009-09-08 | Advanced Cardiovascular Systems, Inc. | Coatings for drug delivery devices |
US6517889B1 (en) * | 2001-11-26 | 2003-02-11 | Swaminathan Jayaraman | Process for coating a surface of a stent |
US6663880B1 (en) | 2001-11-30 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Permeabilizing reagents to increase drug delivery and a method of local delivery |
US6709514B1 (en) | 2001-12-28 | 2004-03-23 | Advanced Cardiovascular Systems, Inc. | Rotary coating apparatus for coating implantable medical devices |
US20040054104A1 (en) | 2002-09-05 | 2004-03-18 | Pacetti Stephen D. | Coatings for drug delivery devices comprising modified poly(ethylene-co-vinyl alcohol) |
US20040063805A1 (en) | 2002-09-19 | 2004-04-01 | Pacetti Stephen D. | Coatings for implantable medical devices and methods for fabrication thereof |
US6818063B1 (en) | 2002-09-24 | 2004-11-16 | Advanced Cardiovascular Systems, Inc. | Stent mandrel fixture and method for minimizing coating defects |
US7087263B2 (en) | 2002-10-09 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Rare limiting barriers for implantable medical devices |
US7482034B2 (en) | 2003-04-24 | 2009-01-27 | Boston Scientific Scimed, Inc. | Expandable mask stent coating method |
US7198675B2 (en) | 2003-09-30 | 2007-04-03 | Advanced Cardiovascular Systems | Stent mandrel fixture and method for selectively coating surfaces of a stent |
US7704544B2 (en) | 2003-10-07 | 2010-04-27 | Advanced Cardiovascular Systems, Inc. | System and method for coating a tubular implantable medical device |
-
2002
- 2002-12-12 US US10/319,042 patent/US7074276B1/en not_active Expired - Lifetime
-
2006
- 2006-05-19 US US11/437,589 patent/US7648725B2/en not_active Expired - Fee Related
- 2006-05-19 US US11/437,593 patent/US7572336B2/en not_active Expired - Fee Related
-
2009
- 2009-12-11 US US12/636,301 patent/US7901728B2/en not_active Expired - Fee Related
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1133334A (en) * | 1912-06-18 | 1915-03-30 | Detroit Dental Mfg Company | Work-holding tool. |
US1333334A (en) * | 1918-04-05 | 1920-03-09 | Warren Hines Nesmith | Gin or delinting-gin |
US1346584A (en) * | 1920-04-15 | 1920-07-13 | Edward H Angle | Orthodontic implement |
US3226245A (en) * | 1958-02-05 | 1965-12-28 | Polymer Corp | Coating method and apparatus |
US5716981A (en) * | 1993-07-19 | 1998-02-10 | Angiogenesis Technologies, Inc. | Anti-angiogenic compositions and methods of use |
Also Published As
Publication number | Publication date |
---|---|
US7572336B2 (en) | 2009-08-11 |
US20060207501A1 (en) | 2006-09-21 |
US7074276B1 (en) | 2006-07-11 |
US20060210702A1 (en) | 2006-09-21 |
US7648725B2 (en) | 2010-01-19 |
US7901728B2 (en) | 2011-03-08 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7901728B2 (en) | Clamp mandrel fixture and a method of using the same to minimize coating defects | |
US6955723B2 (en) | Mandrel for supporting a stent and method of using the mandrel to coat a stent | |
US6572644B1 (en) | Stent mounting device and a method of using the same to coat a stent | |
US6527863B1 (en) | Support device for a stent and a method of using the same to coat a stent | |
US7258891B2 (en) | Stent mounting assembly and a method of using the same to coat a stent | |
US7794777B2 (en) | Method for reducing stent coating defects | |
US8689729B2 (en) | Apparatus for coating stents | |
US7485333B2 (en) | Method of using a stent mounting device to coat a stent | |
US7485334B2 (en) | Stent mandrel fixture and method for minimizing coating defects | |
US8312837B2 (en) | Support assembly for stent coating | |
US8007856B2 (en) | Mounting assembly for a stent and a method of using the same to coat a stent | |
US8042485B1 (en) | Stent mandrel fixture and method for coating stents |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCF | Information on status: patent grant |
Free format text: PATENTED CASE |
|
FPAY | Fee payment |
Year of fee payment: 4 |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 8TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1552); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Year of fee payment: 8 |
|
FEPP | Fee payment procedure |
Free format text: MAINTENANCE FEE REMINDER MAILED (ORIGINAL EVENT CODE: REM.); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY |
|
LAPS | Lapse for failure to pay maintenance fees |
Free format text: PATENT EXPIRED FOR FAILURE TO PAY MAINTENANCE FEES (ORIGINAL EVENT CODE: EXP.); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY |
|
STCH | Information on status: patent discontinuation |
Free format text: PATENT EXPIRED DUE TO NONPAYMENT OF MAINTENANCE FEES UNDER 37 CFR 1.362 |
|
FP | Lapsed due to failure to pay maintenance fee |
Effective date: 20230308 |